Single-chamber leadless intra-cardiac medical device with dual-chamber functionality and shaped stabilization intra-cardiac extension

ABSTRACT

A leadless intra-cardiac medical device (LIMD) configured to be implanted entirely within a heart of a patient includes a housing configured to be securely attached to an interior wall portion of a chamber of the heart, and a stabilizing intra-cardiac (IC) device extension connected to the housing. The stabilizing IC device extension may include a stabilizer arm, and/or an appendage arm, or an elongated body or a loop member configured to be passively secured within the heart.

CROSS REFERENCE TO RELATED APPLICATIONS

This application relates to and claims priority benefits from U.S.Provisional Application No. 61/555,390, filed Nov. 3, 2011, entitled“Single Chamber Leadless Implantable Medical Device with Dual ChamberFunctionality and Shaped Stabilization Appendage,” which is herebyincorporated by reference in its entirety. This application also relatesto U.S. patent application Ser. No. 13/352,048, filed Jan. 17, 2012,entitled “Single-Chamber Leadless Intra-Cardiac Medical Device withDual-Chamber Functionality,” and Ser. No. 13/352,136, filed Jan. 17,2012, entitled “Dual-Chamber Leadless Intra-Cardiac Medical Device withIntra-Cardiac Extension,” which are hereby incorporated by reference intheir entirety.

FIELD OF THE INVENTION

Embodiments of the present invention generally relate to implantablemedical devices, and more particularly to leadless intra-cardiac medicaldevices that afford dual chamber functionality from a position within asingle chamber of the heart. As used herein, the term “leadless”generally refers to an absence of electrically-conductive leads thattraverse vessels or other anatomy outside of the intra-cardiac space,while “intra-cardiac” means generally, entirely within the heart andassociated vessels, such as the SVC, IVC, CS, pulmonary arteries and thelike.

BACKGROUND OF THE INVENTION

Current implantable medical devices (IMD) for cardiac applications, suchas pacemakers, include a “housing” or “can” and one or moreelectrically-conductive leads that connect to the can through anelectro-mechanical connection. The can is implanted outside of theheart, in the pectoral region of a patient and contains electronics(e.g., a power source, microprocessor, capacitors, etc.) that providepacemaker functionality. The leads traverse blood vessels between thecan and heart chambers in order to position one or more electrodescarried by the leads within the heart, thereby allowing the deviceelectronics to electrically excite or pace cardiac tissue and measure orsense myocardial electrical activity.

To sense atrial cardiac signals and to provide right atrial chamberstimulation therapy, the can is coupled to an implantable right atriallead including at least one atrial tip electrode that typically isimplanted in the patient's right atrial appendage. The right atrial leadmay also include an atrial ring electrode to allow bipolar stimulationor sensing in combination with the atrial tip electrode.

Before implantation of the can into a subcutaneous pocket of thepatient, however, an external pacing and measuring device known as apacing system analyzer (PSA) is used to ensure adequate lead placement,maintain basic cardiac functions, and evaluate pacing parameters for aninitial programming of the IMD. In other words, a PSA is a systemanalyzer that is used to test an implantable device, such as animplantable pacemaker.

To sense the left atrial and left ventricular cardiac signals and toprovide left-chamber stimulation therapy, the can is coupled to the“coronary sinus” lead designed for placement in the “coronary sinusregion” via the coronary sinus ostium in order to place a distalelectrode adjacent to the left ventricle and additional electrode(s)adjacent to the left atrium. As used herein, the phrase “coronary sinusregion” refers to the venous vasculature of the left ventricle,including any portion of the coronary sinus, great cardiac vein, leftmarginal vein, left posterior ventricular vein, middle cardiac vein,and/or small cardiac vein or any other cardiac vein accessible by thecoronary sinus.

Accordingly, the coronary sinus lead is designed to: receive atrialand/or ventricular cardiac signals; deliver left ventricular pacingtherapy using at least one left ventricular tip electrode for unipolarconfigurations or in combination with left ventricular ring electrodefor bipolar configurations; deliver left atrial pacing therapy using atleast one left atrial ring electrode as well as shocking therapy usingat least one left atrial coil electrode.

To sense right atrial and right ventricular cardiac signals and toprovide right-chamber stimulation therapy, the can is coupled to animplantable right ventricular lead including a right ventricular (RV)tip electrode, a right ventricular ring electrode, a right ventricularcoil electrode, a superior vena cava (SVC) coil electrode, and so on.Typically, the right ventricular lead is inserted transvenously into theheart so as to place the right ventricular tip electrode in the rightventricular apex such that the RV coil electrode is positioned in theright ventricle and the SVC coil electrode will be positioned in theright atrium and/or superior vena cava. Accordingly, the rightventricular lead is capable of receiving cardiac signals, and deliveringstimulation in the form of pacing and shock therapy to the rightventricle.

Although a portion of the leads, as well as the IMD itself are outsideof the patient's heart. Consequently, bacteria and the like may beintroduced into the patient's heart through the leads, as well as theIMD, thereby increasing the risk of infection within the heart.Additionally, because the IMD is outside of the heart, the patient maybe susceptible to Twiddler's syndrome, which is a condition caused bythe shape and weight of the IMD itself. Twiddler's syndrome is typicallycharacterized by a subconscious, inadvertent, or deliberate rotation ofthe IMD within the subcutaneous pocket formed in the patient. In oneexample, a lead may retract and begin to wrap around the IMD. Also, oneof the leads may dislodge from the endocardium and cause the IMD tomalfunction. Further, in another typical symptom of Twiddler's syndrome,the IMD may stimulate the diaphragm, vagus, or phrenic nerve, pectoralmuscles, or brachial plexus. Overall, Twiddler's syndrome may result insudden cardiac arrest due to conduction disturbances related to the IMD.

In addition to the foregoing complications, leads may experience certainfurther complications, such as incidences of venous stenosis orthrombosis, device-related endocarditis, lead perforation of thetricuspid valve and concomitant tricuspid stenosis; and lacerations ofthe right atrium, superior vena cava, and innominate vein or pulmonaryembolization of electrode fragments during lead extraction.

To combat the foregoing limitations and complications, small sizeddevices configured for intra-cardiac implant have been proposed. Thesedevices, termed leadless pacemakers (LLPM) are typically characterizedby the following features: they are devoid of leads that pass out of theheart to another component, such as a pacemaker outside of the heart;they include electrodes that are affixed directly to the “can” of thedevice; the entire device is attached to the heart; and the device iscapable of pacing and sensing in the chamber of the heart where it isimplanted.

LLPM devices that have been proposed thus far offer limited functionalcapability. These LLPM devices are able to sense in one chamber anddeliver pacing pulses in that same chamber, and thus offer singlechamber functionality. For example, an LLPM device that is located inthe right atrium would be limited to offering AAI mode functionality. AnAAI mode LLPM can only sense in the right atrium, pace in the rightatrium and inhibit pacing function when an intrinsic event is detectedin the right atrium within a preset time limit. Similarly, an LLPMdevice that is located in the right ventricle would be limited tooffering VVI mode functionality. A VVI mode LLPM can only sense in theright ventricle, pace in the right ventricle and inhibit pacing functionwhen an intrinsic event is detected in the right ventricle within apreset time limit. To gain widespread acceptance by clinicians, it wouldbe highly desired for LLPM devices to have dual chamber pacing/sensingcapability (DDD mode) along with other features, such as rate adaptivepacing.

It has been proposed to implant sets of multiple LLPM devices within asingle patient, such as one or more LLPM devices located in the rightatrium and one or more LLPM devices located in the right ventricle. Theatrial LLPM devices and the ventricular LLPM devices wirelesslycommunicate with one another to convey pacing and sensing informationthere between to coordinate pacing and sensing operations between thevarious LLPM devices.

However, these sets of multiple LLPM devices experience variouslimitations. For example, each of the LLPM devices must expendsignificant power to maintain the wireless communications links. Thewireless communications links should be maintained continuously in orderto constantly convey pacing and sensing information between, forexample, atrial LLPM device(s) and ventricular LLPM device(s). Thispacing and sensing information is necessary to maintain continuoussynchronous operation, which in turn draws a large amount of batterypower.

Further, it is difficult to maintain a reliable wireless communicationslink between LLPM devices. The LLPM devices utilize low powertransceivers that are located in a constantly changing environmentwithin the associated heart chamber. The transmission characteristics ofthe environment surrounding the LLPM device change due in part to thecontinuous cyclical motion of the heart and change in blood volume.Hence, the potential exists that the communications link is broken orintermittent.

SUMMARY OF THE INVENTION

In accordance with one embodiment, a leadless intra-cardiac medicaldevice (LIMD) is provided with dual chamber functionality, withoutleads, despite the fact that the entire device is located in onechamber. In one embodiment, the LIMD stimulates and senses the rightatrium (RA) and right ventricle (RV) chambers, even though it isentirely located in the RA. The electrodes enable delivering stimulusand sensing in different chambers of the heart and thus providephysiological synchronization of myocardial contraction in multiplechambers.

In another embodiment, an LIMD is provided that may be located in theRV, deliver stimulus and sense either the RA or the left ventricle (LV).Alternatively, the LIMD may be located in the RA and configured toelectrically stimulate the RV and LV. This last LLPM configuration orplacement may be done in a manner such that Hisian or para-Hisian pacingis achieved.

In accordance with an embodiment, a leadless intra-cardiac medicaldevice (LIMD) is provided, comprised of a housing configured to beimplanted entirely within a single local chamber of the heart, the localchamber having local wall tissue that constitutes part of a conductionnetwork of the local chamber. A base is provided on the housing, thebase configured to be secured to a septum that separates the localchamber from an adjacent chamber, the adjacent chamber having distalwall tissue, with respect to the local chamber that constitutes part ofa conduction network of the adjacent chamber. A first electrode isprovided at a first position on the base such that, when the device isimplanted in the local chamber, the first electrode engages wall tissueat a local activation site within the conduction network of the localchamber. A second electrode is provided at a second position on the baseand extending outward such that, when the device is implanted in thelocal chamber, the second electrode engages wall tissue at a distalactivation site within the conduction network of the adjacent chamber. Acontroller is provided within the housing to cause stimulus pulses to bedelivered, in a synchronous manner, through the first and secondelectrodes to the local and distal activation sites, respectively, suchthat stimulus pulses delivered at the distal activation site are timedto cause contraction of the adjacent chamber in a predetermined relationto contraction of the local chamber. Optionally, the controller isconfigured to control delivery of the stimulus pulses from the first andsecond electrodes in accordance with a DDD pacing mode or a DDDR pacingmode.

The septum may represent a portion of the tricuspid annulus. The base ofthe housing is configured to engage an activation site on the tricuspidannulus. The second electrode delivers stimulus pulses to the tricuspidannulus to initiate activation in a right ventricle. The controller maybe configured to control delivery, from the first and second electrodes,of the stimulus pulses to a right atrium and a right ventricle, whilethe LIMD is entirely located in one of the right atrium and rightventricle.

The distal wall tissue constitutes wall tissue of at least one of a leftatrium, a right ventricle, and a left ventricle. The distal wall tissueis physiologically responsive to distal activation events originating inthe at least one of left atrium, right ventricle, and left ventricle.

In accordance with an embodiment, the housing may also include anextension arm having the first electrode located on a distal endthereof. The extension arm may be configured to extend into and engagethe local wall tissue in an appendage area of the local chamber.Optionally, the housing may also include an extension arm and astabilization arm joined to a top end of the housing. The extension armmay have the first electrode located on a distal end thereof to extendinto and engage the local wall tissue in an appendage area of the localchamber. The stabilization arm may have a distal end that extends to andengages an opposed stabilization area of the local chamber. Thestabilization arm may have a distal end that extends to and engages asuperior vena cava of the heart. The extension arm and a stabilizationarm may be pivotally joined to a hinge assembly located at a top end ofthe housing. The extension arm and a stabilization arm may be securelyjoined to a top end of the housing. The extension arm and stabilizationarm may be biased to flare outward away from one another when in adeployed position such that distal ends of the stabilization andextension arms engage the local chamber in opposed areas remote from thebase of the housing.

Certain embodiments provide a leadless intra-cardiac medical deviceconfigured to be implanted entirely within a heart of a patient. Thedevice may include a housing and a stabilizing intra-cardiacintra-cardiac device extension. The housing is configured to be securelyattached to an interior wall portion of a chamber of the heart. Theextension is connected to the housing, and is configured to be passivelysecured within the heart.

The extension may include a loop member. The loop member is configuredto be passively secured within one or both of the chamber of the heartor a superior vena cava of the heart. The loop member may include firstand second loops connected to one another. Each of the first and secondloops may have a perimeter that flares in a lateral direction withrespect to a longitudinal axis of the loop body. The loop member mayinclude a perimeter shaped as a disc, oval, circle, tube, rectangle, ortriangle.

The loop member may include a plurality of interconnected loops. Each ofthe plurality of interconnected loops may be commonly aligned andoriented with respect to one another. The plurality of interconnectedloops may include a first loop and a second loop. The first loop may beoriented orthogonal to the second loop.

A first of the plurality of interconnected loops may be aligned in afirst orientation and a second of the plurality of interconnected loopsmay be aligned in a second orientation. The first orientation differsfrom the second orientation so that the first and second of theplurality of interconnected loops are oriented out of plane with oneanother.

The device may also include at least one electrode secured to the loopmember. The electrode is configured to contact tissue within the heart,and provide one or both of sensing or stimulus.

The device may also include at least one radio marker secured to theloop member. The radio marker is configured to allow the LIMD system tobe tracked within patient anatomy.

The device may also include an anchoring member extending from a distalend. The anchoring member is configured to securely anchor the housingto tissue within the heart. The anchoring member may include a securinghelix. The securing helix may serve as an electrode.

In an embodiment, the stabilizing intra-cardiac device extension mayinclude a first curved portion with respect to the housing. The firstcurved portion may be connected to a first linear region that connectsto a second curved portion. The first curved portion may beapproximately 90 degrees with respect to the housing. The second curvedportion may be approximately 180 degrees away from the housing. Thesecond curved portion may connect to a second linear region thatconnects to a third curved portion. The second curved portion may beconfigured to be implanted within a right atrial appendage of the heart.An electrode may be located proximate a junction of the second curvedportion and the second linear region. The third curved portion may forman extending arc that approximates a 90 degree turn away from thehousing that terminates at a tail end.

Certain embodiments provide a method of implanting a leadlessintra-cardiac medical device (LIMD) entirely within a heart of apatient. The device includes a housing and a stabilizing intra-cardiacdevice extension connected to the housing. The method may includenavigating the device into the heart with an introducer assembly, theextension held in a collapsed installation shape within the introducerassembly, positioning the introducer assembly so that the housing isproximate an implant site within the heart, securely anchoring thehousing to the implant site, separating the introducer assembly and thedevice, thereby allowing the extension to expand to a deployed implantedshape, and securing the extension within a portion of the heart so thatthe device is entirely within the heart of the patient.

In accordance with embodiments herein, the stabilizing intra-cardiacdevice extension comprises an elongated body, and expanding includespermitting the elongated body to expand to a pre-loaded shape in which afirst curved segment bends at an angle with respect to a longitudinalaxis of the housing, wherein the first curved segment merges into afirst linear region that extends laterally from the housing toward atissue of interest, the elongated body including an electrode providedthereon at a position configured to contact the tissue of interest.

In accordance with optional embodiments herein, the stabilizingintra-cardiac device extension comprises an elongated body, andexpanding includes permitting the elongated body to expand to apre-loaded shape such that a first linear region extends laterally fromthe housing, along a lateral axis, and merges with a second curvedsegment, the second curved segment turning at an angle with respect to alongitudinal axis of the housing and a lateral axis of the first linearregion.

In accordance with other embodiments herein, the stabilizingintra-cardiac device extension comprises an elongated body, andexpanding includes permitting the elongated body to expand to apre-loaded shape in which first and second linear regions are joined toone another through a curved segment, the method further comprisingpositioning the first linear region and the curved segment to extendinto a right atrial appendage, and positioning the second linear regionto extend from the right atrial appendage toward the SVC.

In accordance with embodiments herein, the extension comprises anelongated body that includes first and second curved segments joined toone another by a linear region, at least one of the first and secondcurved segments including an electrode, the method further comprisingpositioning the electrode to contact tissue of interest.

In accordance with embodiments herein, the extension comprises anelongated body that is tubular in shape and includes a metal braid, themethod further comprising applying at least one of rotational andlongitudinal pressure upon the IC device extension, the braid resistingrotational torque and longitudinal compression to facilitate delivery ofrotational forces and longitudinal pressure to the housing of thedevice.

Optionally, the method may comprise guiding the extension to engage afirst region of the heart, the first region representing at least one ofa superior vena cava, an inferior vena cava, a coronary sinus, and apulmonary artery. Optionally, the extension may include a stabilizerend-segment that is pre-formed to bend at an angle and fit against aninterior of at least one of a superior vena cava, an inferior vena cava,a coronary sinus, and a pulmonary artery.

In accordance with embodiments herein, the method may comprisingconfiguring a controller of the device to control delivery of stimuluspulses from first and second electrodes in accordance with a DDD pacingmode to a right atrium and right ventricle, while the device is entirelylocated in one of the right atrium and right ventricle.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 illustrates a sectional view of a patient's heart with a leadlessintra-cardiac medical device (LIMD) implanted therein.

FIG. 2 illustrates a right anterior oblique view representing theinterior surface of the right atrium wall.

FIG. 3A illustrates a side perspective view of the LIMD of FIG. 1oriented with the base facing upward to illustrate electrodes in moredetail.

FIG. 3B illustrates a bottom plan view of the LIMD of FIG. 3A.

FIG. 3C illustrates examples of locations where an LIMD may beimplanted.

FIG. 4A illustrates a LIMD that has a base with spikes extending therefrom.

FIG. 4B illustrates a LIMD that has a base with serrated edges thatproject outward from the base.

FIG. 4C illustrates a LIMD that has a base with a fixation mechanismsimilar to a pair of large diameter double-helix, but with a positivedeflection near the base.

FIG. 4D illustrates a LIMD that has a base with a fixation mechanismthat has a screw wire with different thickness at the proximal anddistal ends.

FIG. 4E illustrates a LIMD that has a base with a fixation mechanismthat has a screw wire with different diameter at the proximal and distalends.

FIG. 4F illustrates a LIMD with a variation in the fixation mechanismshown in FIG. 4C.

FIG. 4G illustrates a LIMD with a helical cathode electrode thatsurrounds a long spike electrode.

FIG. 5A illustrates a LIMD formed in accordance with an alternativeembodiment, including an appendage arm and a stabilizer arm.

FIG. 5B illustrates the LIMD of FIG. 5A during installation, whilerotated within an introducer.

FIG. 5C illustrates the LIMD of FIG. 5A in an exemplary deployedposition within a heart.

FIG. 6A illustrates a LIMD formed in accordance with an alternativeembodiment, in which the appendage arm and stabilizer arm are configuredin a manner different than those of FIG. 5A.

FIG. 6B illustrates the LIMD of FIG. 6A during installation, whilelocated within an introducer.

FIG. 6C illustrates the LIMD of FIG. 6A in an exemplary deployedposition within a heart.

FIG. 7A illustrates an alternative embodiment for a LIMD in a collapsedinstallation configuration.

FIG. 7B illustrates the LIMD of FIG. 7A in a deployed flared position.

FIG. 8 illustrates an exemplary block diagram of the electricalcomponents of an LIMD.

FIG. 9A illustrates a sectional view of a patient's heart and a LIMDhaving a shaped intra-cardiac (IC) device extension.

FIG. 9B illustrates a model of an interior of a canine heart and a LIMDhaving a shaped IC device extension.

FIG. 9C further illustrates a model of an interior of a human heart andshows an example of the LIMD having the shaped IC device extensiondescribed with reference to FIG. 9A.

FIG. 9D further illustrates a model of an interior of a human heart andshows an example of the LIMD having the shaped IC device extensiondescribed with reference to FIG. 9A.

FIG. 9E provides an enlarged view of a portion of a shaped IC deviceextension, while in the right atrial appendage.

FIG. 9F illustrates a longitudinal axial view of an introducer assembly,with the LIMD including the IC device extension of FIG. 9A insertedtherein.

FIG. 9G illustrates a cross section of a portion of an IC deviceextension according to an embodiment.

FIG. 10 illustrates an embodiment of a LIMD.

FIG. 11 illustrates a LIMD introducer assembly with the LIMD of FIG. 10inserted therein.

FIG. 12 illustrates the LIMD of FIG. 10 implanted within a heart of apatient.

FIG. 13 illustrates another embodiment of an LIMD.

FIG. 14 illustrates the LIMD of FIG. 13 implanted within a heart of apatient.

DETAILED DESCRIPTION

Dual-chamber permanent pacemakers (PPM), operating in the DDD or DDDRmode, are indicated for patients with complete atrioventricular (AV)block, sick sinus syndrome, and paroxysmal AV block. The use of DDD orDDDR mode PPMs in patients with a high degree of AV block is shown toimprove subjective metrics of patient life and increase peak velocityand cardiac output, compared to VVIR PPMs. Additionally, another studydemonstrates reduced incidence of atrial fibrillation (AF) and increasedpatient longevity in patients with sick sinus syndrome after the time ofDDDR PPM implant. These significant benefits, accrued to the threepreviously-described subgroups of implant patients, provide a strongimpetus for using DDDR PPMs in those recipients.

The benefits of conventional DDD or DDDR PPMs are counterbalanced by theincreased risk of complications with the additional lead necessary forthese PPMs (compared to single-chamber devices). A preferred solution tothis dilemma as offered by embodiments herein eliminate the need to useleads by providing an LIMD with DDDR mode functionality. As a result,patients suffering from various degrees of AV block or sick sinussyndrome may receive dual-chamber pacing therapy without an increasedrisk of complications (such as lead-associated infections caused bybiofilm formation 14 or explant-related difficulties). In particular,decreased incidence of device-related infections may be achieved by aDDDR mode-capable LIMD as a result of the device body's small surfacearea (compared to conventional PPMs and leads), which presents a reducedsubstrate for bacterial or fungal adhesion.

Myocardial contraction results from a change in voltage across the cellmembrane (depolarization), which leads to an action potential. Althoughcontraction may happen spontaneously, it is normally in response to anelectrical impulse. In normal physiologic behavior, this impulse startsin the sino-atrial (SA) node where a collection of cells are located atthe junction of the right atrium and superior vena cava. Thesespecialized cells depolarize spontaneously, and cause a wave ofcontraction to follow a conduction network along the tissue wall of theatria. Following atrium contraction, the impulse is delayed at theatrio-ventricular (AV) node, located in the septum wall of the rightatrium. From here HIS-Purkinje fibers allow rapid conduction of theelectrical impulse to propagate along the conduction network formed bythe right and left branches in the RV and LV tissue walls, causingalmost simultaneous depolarization of both ventricles, approximately 0.2seconds after the initial impulse has arisen in the sino-atrial node.Depolarization of the myocardial cell membrane causes a large increasein the concentration of calcium within the cell, which in turn causescontraction by a temporary binding between two proteins, actin andmyosin. The cardiac action potential is much longer than that ofskeletal muscle, and during this time the myocardial cell isunresponsive to further excitation. Hence, in a general sense, thetissue walls of each chamber constitute part of a conduction network ofthe corresponding chamber.

FIG. 1 provides a sectional view of a patient's heart 33 and shows aleadless intra-cardiac medical device 300. The leadless implantablemedical device 300 has been placed through the superior vena cava 28into the right atrium 30 of the heart 33. FIG. 1 also shows the inferiorvena cava 35, the left atrium 36, the right ventricle 37, the leftventricle 40, the atrial septum 41 that divides the two atria 30, 36,the ventricular vestibule VV, the right atrial appendage (RAA), and thetricuspid valve 42 between the right atrium 30 and right ventricle 37.The reader will appreciate that the view of FIG. 1 is simplified andsomewhat schematic, but that nevertheless FIG. 1 and the other viewsincluded herein will suffice to illustrate adequately the placement andoperation of embodiments of the present invention. The term “septum”shall be used throughout to generally refer to any portion of the heartseparating two chambers (e.g. RA to LA, RV to LV). The leadlessimplantable medical device (LIMD) 300 is formed in accordance with anembodiment. The LIMD 300 may represent a pacemaker that functions in aDDD mode or a DDDR-mode, a cardiac resynchronization device, acardioverter, a defibrillator and the like. When in DDD or DDDR-mode,the LIMD 300 may sense in two chambers, pace in two chambers and inhibitpacing in either chamber based on intrinsic events sensed in thatchamber or in the other chamber. The LIMD 300 comprises a housingconfigured to be implanted entirely within a single local chamber of theheart. For example, the LIMD 300 may be implanted entirely and solelywithin the right atrium or entirely and solely within the rightventricle. Optionally, the LIMD 300 may be implanted entirely and solelywithin the left atrium or left ventricle through more invasive implantmethods.

For convenience, hereafter the chamber in which the LIMD 300 isimplanted shall be referred to as the “local” chamber. The local chamberincludes a local chamber wall that is physiologically response to localactivation events originating in the local chamber. The local chamber isat least partially surrounded by local wall tissue that forms orconstitutes at least part of a conduction network for the associatedchamber. For example, during normal operation, the wall tissue of theright atrium contracts in response to an intrinsic local activationevent that originates at the sinoatrial (SA) node and in response toconduction that propagates along the atrial wall tissue. For example,tissue of the right atrium chamber wall in a healthy heart follows aconduction pattern, through depolarization, that originates at the SAnode and moves downward about the right atrium until reaching the atriaventricular (AV) node. The conduction pattern moves along the chamberwall as the right atrium wall contracts.

The term “adjacent” chamber shall refer to any chamber separated fromthe local chamber by tissue (e.g., the RV, LV and LA are adjacentchambers to the RA; the RA and LV are adjacent chambers to the LA; theRA and RV are adjacent to one another; the RV and LV are adjacent to oneanother, and the LV and LA are adjacent to one another).

The local chamber (e.g., the right atrium) has various tissue ofinterest, such as a septum, that separate the local chamber from theadjacent chambers (e.g., right ventricle, left atrium, left ventricle).In certain portions or segments of the septum, segments of the septum,behave in physiologically different manners. For example, in certainsegments of the septum for the right atrium, even during normal healthyoperation, the septum wall tissue does not propagate the conduction inthe same manner or pattern as in a majority of the wall tissue of theright atrium wall. For example, septum wall tissue in the right atrium,referred to as the ventricular vestibule tissue, does not behavephysiologically in the same manner as the non-septum atrial wall tissue.Instead, the right ventricular vestibule tissue is physiologicallycoupled to the wall tissue in the right ventricle and in accordancetherewith exhibits a conduction pattern that follows the conductionpattern of the right ventricular wall tissue. The right ventricularvestibule tissue is one example of a septum segment that partiallyseparates a local chamber (e.g., the right atrium) from an adjacentchamber (e.g., right ventricle), yet is physiologically coupled toconduction in the adjacent chamber (e.g., right ventricle).

In the example of FIG. 1, the LIMD 300 is implanted in an area neardifferent regions of tissue that follow the conductive pattern ofdifferent chambers of the heart. Optionally, the LIMD 300 may beimplanted such that at least one electrode on the base of the LIMD 300engages tissue that is part of the conductive network of the onechamber, while at least one other electrode projects from the base intotissue that is part of the conductive network of another chamber. Forexample, when the LIMD 300 may be implanted within or near the triangleof Koch in an area adjacent the ventricular vestibule. The conductivenetwork of the tissue in the ventricular vestibule follows theconductive pattern of the right ventricle. Therefore, the LIMD 300 maybe implanted near the edge of the triangle of Koch such that one or moreproximal electrodes, extending from the LIMD 300, are electricallycoupled to the conductive network of the right atrium, while one or moreother distal electrodes, extend diagonally to become electricallycoupled to the conductive network of the right ventricle (e.g., theventricular vestibule). Optionally, the LIMD 300 may be positioned withthe base located against the RA wall above the mitral valve, but with adistal electrode that projects into the septum to ventricular tissue ofthe right or left ventricle.

FIGS. 3A and 3B illustrate the LIMD 300 in more detail. FIG. 3Aillustrates a side perspective view of the LIMD 300 of FIG. 1 orientedwith the base 304 facing upward to illustrate electrodes 310-312 in moredetail. FIG. 3B illustrates a bottom plan view of the LIMD 300. The LIMD300 comprises a housing 302 having a proximal base 304, a distal top end306, and an intermediate shell 308 extending between the proximal base304 and the distal top end 306. The shell 308 is elongated and tubularin shape and extends along a longitudinal axis 309.

The base 304 includes one or more electrodes 310-312 securely affixedthereto and projected outward. For example, the outer electrodes 310,311 may be formed as large semi-circular spikes or large gauge wiresthat wrap only partially about the inner electrode 312. The electrodes310, 311 may be located on opposite sides of, and wound in a commondirection with, the inner electrode 312. The first or outer electrodes310, 311 are provided directly on the housing 302 of the LIMD 300 at afirst position, namely at or proximate a periphery of the base 304 ofthe housing. The outer electrodes 310, 311 are positioned near theperiphery of the base 304 such that, when the LIMD 300 is implanted inthe local chamber (e.g., right atrium), the outer electrodes 310, 311engage the local chamber wall tissue at tissue of interest for a localactivation site that is near the surface of the wall tissue, and that iswithin the conduction network of the local chamber. The outer electrodes310, 311 are physically separated or bifurcated from one another andhave separate distal outer tips 315, 316. The outer electrodes 310, 311are electrically joined to one another (i.e., common), but areelectrically separated from the inner electrode 312.

The second or inner electrode 312 is also provided directly on thehousing 302 of the LIMD 300 at a second position, namely at or proximateto a central portion of the base 304 of the housing. The inner electrode312 is positioned near the center of the base 304 and is elongated suchthat, when the LIMD 300 is implanted in the local chamber, the innerelectrode 312 extends a majority of the way through the wall tissue(e.g. septum) until reaching tissue of interest near the adjacentchamber wall. The inner electrode 312 is inserted to a depth such that adistal tip thereof is located at tissue of interest for an activationsite that is physiologically coupled to wall tissue of the adjacentchamber (e.g. right ventricle). For example, the inner electrode 312 mayextend until the distal tip extends at least partially through a septumto a position proximate to a distal wall tissue within the conductionnetwork of the adjacent chamber. Optionally, the inner electrode 312 maybe inserted at a desired angle until the distal end enters theventricular vestibule. By located the distal tip of the inner electrode312 at an adjacent chamber activation site, the inner electrode 312initiates contraction at a distal activation site within the conductionnetwork of the adjacent chamber without physically locating the LIMD 300in the adjacent chamber. The inner and outer electrodes 310-312 may beformed as multiple cathode electrodes that are actively fixated to themyocardium. The outer cathode electrodes 310, 311 may be configured asscrews with a large pitch (e.g. length between adjacent turns), largediameter and may have a length that is relatively short, while the innerelectrode 312 is configured as a screw with a common or smaller pitch,small diameter and longer length. The screw shape of the outerelectrodes 310, 311 is used to firmly adhere them to the cardiac tissue.The outer electrodes 310, 311 may have very little or no insulationmaterial thereon to facilitate a good electrical connection to localwall tissue along the majority or the entire length of the outerelectrodes 310, 311 for delivering stimulus pulses and sensingelectrical activity in the local chamber where the LIMD 300 is located.

The inner electrode 312 is shaped in a helix or screw and is longer(e.g., extends a greater distance from the base) than the outerelectrodes 310, 311. The inner electrode 312 is fashioned to anappropriate length that permits it to drill a predetermined distanceinto, or entirely through, the septum at the desired location. Forexample, the inner electrode 312 may be provided with a desired lengthsufficient to extend through, or to a desired distance into, a septumregion separating two chambers of the heart. For example, the outerelectrodes 310, 311 may contact atrial wall tissue within the triangleof Koch, while the inner electrode 312 extends diagonally along theseptum into the ventricular vestibule.

The inner electrode 312 may be formed as a single conductive wire or abundle of conductive wires, where a proximal portion of the wire iscovered with insulation, while the distal tip 314 is covered withinsulation and is exposed. By covering the proximal portion of theelectrode 312 with insulation, this limits electrical conduction of theconductive wire to tissue surrounding the distal tip 314. Whenimplanted, the distal tip 314 of the electrode is located far below thesurface tissue of the chamber wall in which the LIMD 300 is located. Asa consequence, the distal tip 314 of the inner electrode 312 directlyengages or is located proximate to the surface tissue of an adjacentchamber wall. Hence, the distal tip will 314 senses electrical activityfrom the conductive network of the adjacent chamber that isrepresentative of physiologic behavior (e.g., conduction pattern) of theadjacent chamber. Also, when delivering stimulus pulses, the distal tip314 will deliver the pulses into the conductive network of the adjacentchamber wall.

The combination of the inner and outer screw type electrodes 310-312also imparts extra mechanical stability to the LIMD 300, preventingunwanted torque and shear effects as the heart wall moves duringcontraction. Otherwise, such effects would otherwise predispose the LIMD300 to dislodgement. Extraction could simply entail a combination ofunscrewing of the two cathodes in conjunction with a slight tuggingforce directed away from the myocardial wall.

Optionally, a single anode electrode or multiple anode electrodes 318may be provided. The anode electrode(s) 318 may be located along one ormore sides of the shell 308, and/or on the top end 306 of the LIMD 300.

The LIMD 300 includes a charge storage unit 324 and sensing circuit 322within the housing 302. The sensing circuit 322 senses intrinsicactivity, while the change storage unit 324 stores high or low energyamounts to be delivered in one or more stimulus pulses. The electrodes310-312 may be used to deliver lower energy or high energy stimulus,such as pacing pulses, cardioverter pulse trains, defibrillation shocksand the like. The electrodes 310-312 may also be used to senseelectrical activity, such as physiologic and pathologic behavior andevents and provide sensed signals to the sensing circuit 322. Theelectrodes 310-312 are configured to be joined to an energy source, suchas a charge storage unit 324. The electrodes 310-312 receive stimuluspulse(s) from the charge storage unit 324. The electrodes 310-312 may bethe same or different size. The electrodes 310-312 are configured todeliver high or low energy stimulus pulses to the myocardium.

The LIMD 300 includes a controller 320, within the housing 302 to causethe charge storage unit 324 to deliver activation pulses through each ofthe electrodes 310-312 in a synchronous manner, based on informationfrom the sensing circuit 322, such that activation pulses delivered fromthe inner electrode 312 are timed to initiate activation in the adjacentchamber. The stimulus pulses are delivered synchronously to local anddistal activation sites in the local and distal conduction networks suchthat stimulus pulses delivered at the distal activation site are timedto cause contraction of the adjacent chamber in a predetermined relationto contraction of the local chamber. The inner and outer electrodes310-312 are spaced radially and longitudinally apart from one anothersuch that the local activation site (e.g., right atrium) and the distalactivation side in the adjacent chamber (e.g., right ventricle) aresufficiently remote from one another within the heart's conductivenetwork to initiate activation in different branches of the heartsconductive network in a time relation that corresponds to the normalhemodynamic timers (e.g. AV delay).

FIG. 2 illustrates a right anterior oblique view representing theinterior surface of the right atrium wall. As shown in FIG. 2, the rightatrium wall includes the superior vena cava (SVC) inlet 202, the fosaovalis 204, coronary sinus 206, IVC 208, tricuspid valve 210 andtricuspid annulus 212 that surrounds the tricuspid valve 210. The LIMD300 may be implanted in various locations within the RA. For example,the LIMD 300 may be implanted in region 214 which is located immediatelyadjacent the coronary sinus 206. Region 214 may be contained within theTriangle of Koch. For example, the LIMD 300 may be implanted in region216 which may represent the ventricular vestibule in an area locatedadjacent the tricuspid valve 210 along a segment of the tricuspidannulus 212. Region 214 represents a local activation site in the localchamber wall at which contractions may be initiated when stimulus pulsesare delivered to the surface tissue in the region 214. Region 216constitutes a distal activation site at which contractions may beinitiated in the right ventricle when stimulus pulses are delivered inthe region 216.

The controller 320 may operate the LIMD 300 in various modes, such as inselect pacemaker modes, select cardiac resynchronization therapy modes,a cardioversion mode, a defibrillation mode and the like. For example, atypical pacing mode may include DDIR, R, DDOR and the like, where thefirst letter indicates the chamber(s) paced (e.g., A: Atrial pacing; V:Ventricular pacing; and D: Dual-chamber (atrial and ventricular)pacing). The second letter indicates the chamber in which electricalactivity is sensed (e.g., A, V, or D). The code O is used when pacemakerdischarge is not dependent on sensing electrical activity. The thirdletter refers to the response to a sensed electric signal (e.g., T:Triggering of pacing function; I: Inhibition of pacing function; D: Dualresponse (i.e., any spontaneous atrial and ventricular activity willinhibit atrial and ventricular pacing and lone atrial activity willtrigger a paced ventricular response) and O: No response to anunderlying electric signal (usually related to the absence of associatedsensing function)). The fourth letter indicates rate responsive if R ispresent.

As one example, the controller 320 may be configured with DDI, DDO, DDDor DDDR mode-capable and the LIMD 300 would be placed in the RA. Thescrew type electrodes 310, 311 are used to secure it in conductivebranch region 214 (FIG. 2). Conductive branch region 214 is containedwithin the Triangle of Koch and is characterized by more readyactivation of RA tissue compared to conductive branch region 216. Whenthe LIMD 300 is secured in conductive branch region 216, it is possibleto achieve Hisian/para-Hisian pacing from the RA and performbiventricular stimulation that is more consistent with normalphysiology. It may be possible to also perform AV pacing from conductivebranch region 216.

As one example, the conductive branch region 216 represents the adjacentchamber activation site within the ventricular vestibule. The innerelectrode 312 delivers stimulus pulses to the ventricular vestibule toinitiate activation in the right ventricle 37 of the heart. When theLIMD 300 is secured in the conductive branch region septum 216, theinner electrode 312 is located in a minor tissue portion that isnon-responsive to the local events and local conduction occurring in theright atrium. The distal end 314 of the inner electrode 312 electricallyengages the minor tissue portion that is responsive to non-local eventsand non-local conduction originating in another chamber.

The sensing circuit 322 receives sensed signals from one or more of theelectrodes 310-312. The sensing circuit 322 discriminates between sensedsignals that originate in the near field and in the far field. Forexample, the electrodes 310-311 sense electrical potential across smallareas and thereby allow the sensing circuit 322 to discriminate betweendifferent sources of electrical signals. In one embodiment, theelectrode spacing between electrodes 310, 311 is limited or minimized inorder to achieve a select type of sensing such as bipolar sensing whichlimits or minimizes sensing of far field signals. For example, theelectrode 310 may operate as an anode electrode and the electrode 311may operate as a cathode electrode with a small separation there betweensuch that when far field signals (e.g., signals from the rightventricle) reach the first and second electrodes these far field signalsare sensed as a common mode signal with no or a very small potentialdifference between the electrodes.

In another example, an electrode 312 may be provided with a pair ofelectrically separate sensing regions thereon. The sensing regions mayoperate as an anode and as a cathode electrode with a small separationthere between such that when far field signals (e.g., signals from theright atrium) reach the first and second sensing regions these far fieldsignals are sensed as a common mode signal with no or a very smallpotential difference between the sensing regions.

The housing 302 also include a battery 326 that supplies power to theelectronics and energy to the change storage unit 324.

FIG. 3C illustrates some of these possible configurations, namely at350-356. The previous examples involve an LIMD implanted in the RA andcapable of pacing the RV. Optionally, the LIMD may also be located inother locations. At 350, the LIMD is capable of HISian or para-HISianpacing to produce excitation of the RV and LV. When the LIMD isimplanted at 352, the LIMD is able to provide RA/RV sensing and pacingfrom the RA. When the LIMD is implanted at 354, the LIMD is able toprovide RA/RV sensing and pacing from the RV. When the LIMD is implantedat 356, the LIMD is able to provide RV/LV sensing and pacing from theRV. The LIMDs 357, 358, 359 afford LA/RA pacing and sensing, LV/RApacing and sensing, and LV/RV pacing and sensing, respectively. Theseimplementations produce excitation of the RV and LV in a manner moreconsistent with normal physiological function.

FIGS. 4A-4G illustrate various embodiments of fixation mechanisms thatmay be used with an LIMD 400. FIG. 4A illustrates a LIMD 400 that has abase 404 with spikes 410, 411 as cathode electrodes extending therefrom. The spikes 410, 411 are used to fixate the LIMD 400, as well as todeliver stimulus pulses and sense in the local chamber 416 (e.g.atrium). The LIMD 400 also includes an elongated cathode electrode 412that is used for delivering stimulus pulses and for sensing electricalactivity in the conduction network of the adjacent chamber 414 (e.g.,the ventricle). The electrode 412 extends entirely through the chamberwall into the adjacent chamber 414. Optionally, the electrode 412 mayextend near or up to, but not penetrate the wall tissue into theadjacent chamber 414.

FIG. 4B illustrates an LIMD 400 that has a base 404 with an electrodeformed as serrated edges 420 that project outward from the base 404. Theserrated edges 420 form a skirt encircling the base 404. The serratededges 420 are electrically active and can be used for deliveringstimulus pulses and for sensing conductive activity in the local chamber416 as well as fixation. The LIMD 400 also includes an elongated cathodeelectrode 412 that is used for delivering stimulus pulses and forsensing conductive activity in the adjacent chamber 414 (e.g., theventricle).

FIG. 4C illustrates an LIMD 400 that has a base 404 with electrodesformed as a fixation mechanisms 430, 431 similar to a pair of largediameter double-helix, but with a positive deflection 432 near the base404. The purpose of this shape is to ease in the LIMD 400 duringimplant, but rendering unscrewing of the LIMD 400 very difficult due toits firm adhering to the wall. There may also be a single helix thatvaries in diameter or pitch from the proximal end to the distal end,which ensures ease of insertion at implant but causes detachment to bemore difficult as tissue conforms to the helix's shape. The fixationmechanism 430 enclosed in insulation except for a proximal region 433that is exposed and is electrically active in a proximal region near thebase 404 in order to deliver stimulus pulses and to sense conductiveactivity in the local chamber 416. The fixation mechanism 431 is coveredin insulation except for a distal region 435 that is exposed and iselectrically active near the distal end remote from the base 404 inorder to deliver stimulus pulses and to sense conductive activity in theadjacent chamber 414 (e.g., the ventricle).

FIG. 4D illustrates an LIMD 400 that has a base 404 with a fixationmechanism 440 that has a screw non-circular shape with differentcross-sectional thicknesses at the proximal and distal ends 441, 442. Byvarying the cross sectional thickness at different locations along thefixation mechanism 440, this will afford better fixation of the LIMD400. The cross-section may gradually increase or step-wise increasealong the length of the mechanism 440 with greater distance from thebase 404. For example, the fixation mechanism 440 may exhibitprogressively widening cross-section toward the distal end 442 to affordbetter fixation.

FIG. 4E illustrates an LIMD 400 that has a base 404 with a fixationmechanism 450 that has a screw wire shape with different circulardiameter at the proximal and distal ends 451, 452. By varying the wirediameter at different locations along the fixation mechanism 450, thiswill afford better fixation of the LIMD 400. The diameter of the wiremay gradually increase or step-wise increase along the length of themechanism 450 with greater distance from the base 404. The fixationmechanism 450 is formed with two isodiametric sections at the proximaland distal ends 451, 452 which are used to secure the LIMD 400. Forexample, the proximal end 451 may be thinner in diameter, while thedistal end 452 is thicker in diameter.

FIG. 4F illustrates an LIMD 400 with a variation in the fixationmechanism 430, 431 shown in FIG. 4C. In FIG. 4F, the LIMD 400 includesfixation mechanisms 460, 461 with the distal ends 463 of the largedouble-helices having serrated edges 462 that prevent the LIMD 400 fromunscrewing out of the heart chamber wall.

FIG. 4G illustrates an LIMD 400 with a helical cathode electrode 470that surrounds a long spike electrode 471. Once implanted, the spikeelectrode 471 deploys a small mesh 472 similar in shape to an umbrella.The mesh 472 helps secure the LIMD 400 on both ends of the chamber wall.

Optionally, the LIMD 400 may have a single helical active-fixationmechanism that contains one or more passive electrodes on the LIMD 400body that remain in the heart chamber where the LIMD 400 is implanted.The electrode could be brought into contact with the myocardium when thefixation is engaged. The electrodes shown in FIGS. 4A-4G may becathodes, anodes or one of each. Optionally, an anode or cathode may beprovided on the housing of the LIMD 400.

Next alternative embodiments are described in connection with FIGS. 5Ato 7B and FIGS. 9A to 14, in which the LIMD includes an intra-cardiac(IC) device extension. In the embodiments of FIGS. 5A to 7B, the ICdevice extension includes one or both of at least two portions, namely astabilization arm and an appendage arm. In the embodiments of FIGS. 9Ato 14, the IC device extension is formed as a single elongated body thatincludes multiple linear regions and curved segments. The elongated bodyof the IC device extension may have various cross-sectional shapes, suchas disc-shaped, oval, circular, tubular, rectangular, square, polygonal,triangular, and the like. Optionally, the IC device extension may have across-sectional shape that is paddle shaped or flat, semi-circular,donut shaped and the like. The IC device extensions in the embodimentsdescribed herein may be formed from silicon alone, or in combinationwith one or more other materials.

By way of example, the IC device extension may be formed by curing thesilicon such as to a desired crosslink structure to hold a predeterminedshape in which the IC device extension is positioned during curing. Oncethe IC device extension is cured to the desired cross link structure,the IC device extension is retains the predetermined “preload” shape.

FIG. 5A illustrates an LIMD 500 formed in accordance with an alternativeembodiment. The LIMD 500 includes a body or housing 502 having a shell508 that hermetically encloses the electronics, controller, battery,charge storage unit, and all other electrical components of the LIMD500. The housing 502 has a proximal base 504 and a distal top end 506,with the intermediate shell 508 extending there between. The shell 508is elongated and may be tubular in shape to extend along a longitudinalaxis 509. The base 504 includes at least one electrode 512. Theelectrode 512 may be a helical shaped screw to actively secure the base504 at a desired site within a selected local chamber of the heart. Theelectrode 512 includes a conductor that is surrounded by insulationalong the majority of the length thereof, but exposes the distal tip 514of the conductor, such that the electrode 512 only delivers stimuluspulses and senses electrical activity in the region denoted at 515 whichcorresponds to an distal activation site proximate an adjacent chamberwall (and distal from the local chamber in which the LIMD 500 isimplanted).

The LIMD 500 further includes an appendage arm 520 pivotally connectedto and extending outward from the top end 506. The appendage arm 520includes a distal end 522 upon which an electrode 524 is located. Theelectrode 524 may be a passive electrode that is configured to simplyrest against a select activation site. Alternatively, the electrode 524may be an active fixation electrode that is configured to be secured tothe tissue at the activation site (e.g. through a helix, spike, serratededge, barb, and the like).

The appendage arm 520 includes a proximal end 526 that is rotatablycoupled through a hinge assembly 542 to the top end 506 of the housing502. The appendage arm 520 extends along an appendage axis 528 androtates along the appendage rotation arc 544 between limits. The hingeassembly 542 is configured to permit the appendage arm 520 to rotatefrom a collapsed installation position to a deployed implanted position.When in the collapsed position, the appendage arm 520 is rotated in thedirection of arrow 543 until the appendage axis 528 forms a very smallacute angle, or is oriented substantially parallel to, a longitudinalaxis 509 of the shell 508 of the LIMD 500. When in the deployedposition, the appendage arm 520 rotates in the direction of arrow 545until reaching a fully deployed outer limit of the arc of rotation asdefined by the hinge assembly 542. When fully deployed, the appendageaxis 528 projects outward at a larger acute angle (e.g. 10-150°) fromthe longitudinal axis 509 of the shell 508. The outer limit of thedeployed position for the appendage arm 520 is controlled by therotation range permitted at the hinge assembly 542 and may have springtension tensioning it with respect to the stabilizer arm or the housing502.

The LIMD 500 also includes a stabilizer arm 530 having a distal end 532and a proximal end 536. The distal end 532 is formed integral with apusher cup 534 that includes some type of pusher reception feature, suchas a pusher receptacle 540. The pusher cup 534 and receptacle 540 areconfigured to receive an external pusher tool that is used by thephysician when implanting the LIMD 500 (as explained below in moredetail). As one example, the pusher receptacle 540 may include athreaded recess 541 that is configured to threadably and securelyreceive a tip of the pusher tool to ensure a secure attachment to thepusher tool during installation. Once the LIMD 500 is fully implanted,the tip of the pusher tool is unscrewed from the threaded receptacle541. An expandable collet may be used, instead of a screw to attach thepusher tool to the stabilizer arm 530.

The stabilizer arm 530 is rotatably secured, at its proximal end 536, tothe hinge assembly 542 to permit the stabilizer arm 530 to rotate alongarc 546. The stabilizer arm 530 may be rotated between a collapsedinstallation position at which the stabilizer axis 538 is arranged at avery small acute angle or substantially parallel to the longitudinalaxis 509. Once implanted, the stabilizer arm 530 is then permitted torotate outward along arc 546 to a deployed position such that thestabilizer axis 538 forms a larger acute angle (e.g. 10-150°) withrespect to the longitudinal axis 509. The hinge assembly 542 controlsthe range of rotation afforded to the stabilizer arm 530 and may havespring tension tensioning it with respect to the appendage arm 520 orthe housing 502. At least one of the stabilizer arm 530 and appendagearm 520 may be constructed to have a core structure that is torque andcompression resistant such that when the pusher tool is rotated or movedlongitudinally, the stabilizer arm 530 and/or appendage arm 520 conveysrotational and longitudinal force from the pusher tool to the housing ofthe LIMD 500. For example, the core structure may include a metal (e.g.aluminum or stainless steel) braid encased in a biocompatible material,such as PTFE, ETFE or silicon rubber. The braid may have a hollow corein which insulated conductors run between electrodes and the LIMD 500.

Optionally, the stabilizer arm 530 may be fixedly secured to the distalend 506 of the LIMD 500, such that the stabilizer arm 530 does notrotate relative to the longitudinal axis 509. Instead, in thisalternative embodiment, the stabilizer arm 530 is rigidly secured to thedistal end 506 and may be oriented such that the stabilizer axis 530extends directly parallel or at an angle to the longitudinal axis 509 atall times, during installation and after deployment. Again, thestabilizer arm 530 and the appendage arm 520 collectively form an ICdevice extension.

As a further option, a pusher cup or multiple pusher cups 550 may beprovided about the exterior surface of the shell 508 or on the distaltop end 506. The pusher cup 550 includes a pusher receptacle 552configured to receive the tip of a pusher tool that is used duringimplantation. The pusher cup 550 may be provided in place of, or inaddition to, the pusher cup 534. For example, the stabilizer arm 530 maybe entirely removed, in which case the pusher cup 550 may be provided onthe side or top end 506 of the housing 502. Alternatively, when thestabilizer arm 530 is included, but is too flexible to convey rotationaland/or longitudinal force onto the housing 502, then the pusher cup 550may be included. As a further option, pusher cups 534, 550 may both beincluded such as when it is desirable to maintain secure connections tothe housing 502 and the appendage arm 520 and stabilizer arm 530 whilemanipulated and navigated to respective implanted positions. Forexample, once the LIMD 500 is secured to the chamber wall, theintroducer may be partially removed, yet one pusher tool or stylet mayremain secured to the pusher cup 550 to maintain the LIMD 500 in adesired position and orientation while a second tool manipulates theappendage arm 520 and stabilizer arm 530 to implant positions. In thismanner, the tool or stylet in pusher cup 550 prevents excess forces frombeing applied to the electrode 512 while the arms 520, 530 are navigatedto installed positions. Further, the tool or stylet may remain in pushercup 550 until a separate tool is disconnected from pusher cup 534.

Optionally, a third pusher cup could be located on the distal end of theappendage arm 520 to afford direct control over positioning of theelectrode 524.

FIG. 5B illustrates the LIMD 500 of FIG. 5A during installation, whilelocated within an introducer 560. The introducer has a distal end 562that is open to permit the LIMD 500 to be implanted and deployed therethrough. The introducer 560 includes a proximal end 564 along which apusher or other form of tool (e.g. a stylet) is used guide the LIMD 500into position. As shown in FIG. 5B, the stabilizer arm 530 and appendagearm 520 are contracted in their collapsed position to define an outerenvelope substantially no greater than the outer envelope of the body508 of the LIMD 500. The pusher device 562 may engage one or both of thepusher receptacle 540 in the pusher cup 534 and/or the pusher receptacle552 and the pusher cup 550. During implantation, the pusher or stylet562 is securely attached at the receptacle cup 534 to guide the LIMD 500to its activation site. Once the electrode 512 is located against thedesired tissue at the activation site, the pusher or stylet 562 may thenbe rotated to similarly cause the LIMD 500 and electrode 512 to rotateuntil securely affixed within the select tissue. As one example, thereceptacle 540 and/or receptacle 552 may have a noncircular crosssection as viewed from the top down (e.g. a rectangular triangle,hexagon, or other polygon shape) such that when the pusher or stylet 562is rotated, it remains securely fixed within the receptacle 540 toinduce rotation at the electrode 512.

FIG. 6A illustrates an LIMD 600 that resembles the LIMD 500, except thatthe appendage arm 620 and stabilizer arm 630 are configured in a mannerdifferent than those of FIG. 5A. In the embodiment of FIG. 6A, thestabilizer arm 630 and appendage arm 620 are integrally joined with oneanother in a base area 621, but are formed of a flexible material thathas a desired preformed resting shape, corresponding to the deployedconfiguration illustrated in FIG. 6A. When in the deployed position, thestabilizer arms 628, 630 are flared outward away from one another by anangle denoted at 644.

The appendage arm 620 and stabilizer arm 630 have a common proximal end636 that is secured to the top end 606 of the body 602. The appendagearm 620 has a distal end 622 with an electrode 624 thereon as configuredto passively or actively engage tissue at a desired activation site. Thestabilizer arm 630 has a distal end 632 at which a pusher cup 634 isformed integral therewith. The pusher cup 634 includes a pusherreceptacle 640 that is configured to receive a pusher tool duringinstallation. During installation, the appendage arm 620 and stabilizerarm 630 are flexed inward to collapse against one another such that theangle 644 is very small or approximately zero in order that theappendage axis 628 and stabilizer axis 638 extend substantially parallelto the longitudinal axis 609 of the LIMD 600. When the appendage andstabilizer arms 620, 630 are collapsed against one another, the outerenvelope thereof is no greater than the outer envelope of the shell 608to provide a form factor small enough to be received within anintroducer for installation in a desired chamber of the heart.

The LIMD 600 includes a body or housing 602 having a shell 608 thathermetically encloses the electronics, controller, battery, chargestorage unit, and all other electrical components of the LIMD 600. Thehousing 602 has a proximal base 604 and a distal top end 606, with theintermediate shell 608 extending there between. The shell 608 iselongated and may be tubular in shape to extend along a longitudinalaxis 609. The base 604 includes at least one electrode 612. Theelectrode 612 may be a helical shaped screw to actively secure the base604 at a desired site within a selected local chamber of the heart. Theelectrode 612 includes a conductor that is surrounded by insulationalong the majority of the length thereof, but exposes the distal tip 614of the conductor, such that the electrode 612 only delivers stimuluspulses and senses electrical activity in the region denoted at 615 whichcorresponds to an distal activation site proximate to an adjacentchamber wall (and distal from the local chamber in which the LIMD 600 isimplanted).

The LIMD 600 further includes an appendage arm 620 pivotally connectedto and extending outward from the top end 606. The appendage arm 620includes a distal end 622 upon which an electrode 624 is located. Theelectrode 624 may be a passive electrode that is configured to simplyrest against a select activation site. Alternatively, the electrode 624may be an active fixation electrode that is configured to be secured tothe tissue at the activation site (e.g. through a helix, spike, serratededge, barb and the like).

The LIMD 600 also includes a stabilizer arm 630 having a distal end 632and a proximal end 636. The distal end 632 is formed integral with apusher cup 634 that includes some type of pusher reception feature, suchas a pusher receptacle 640. The pusher cup 634 and receptacle 640 areconfigured to receive an external pusher tool that is used by thephysician when implanting the LIMD 600 (as explained below in moredetail). As one example, the pusher receptacle 640 may include athreaded recess 641 that is configured to threadably and securelyreceive a tip of the pusher tool to ensure a secure attachment to thepusher tool during installation. Once the LIMD 600 is fully implanted,the tip of the pusher tool is unscrewed from the threaded receptacle641.

The stabilizer arm 630 may be flexed between a collapsed installationposition at which the stabilizer axis 638 is arranged at a very smallacute angle or substantially parallel to the longitudinal axis 609. Onceimplanted, the stabilizer arm 630 is then permitted to return to itsflared state to a deployed position such that the stabilizer axis 638forms a larger acute angle (e.g. 10-60°) with respect to thelongitudinal axis 609.

Optionally, the stabilizer arm 630 may be fixedly secured to the distalend 606 of the LIMD 600, such that the stabilizer arm 630 does notrotate relative to the longitudinal axis 609. Instead, in thisalternative embodiment, the stabilizer arm 630 is rigidly secured to thedistal end 606 and may be oriented such that the stabilizer axis 630extends directly parallel to the longitudinal axis 609 at all times,during installation and after deployment. Again, the stabilizer arm 630and the appendage arm 620 collectively form an IC device extension.

As a further option, a pusher cup or multiple pusher cups 650 may beprovided about the exterior surface of the shell 608. The pusher cup 650includes a pusher receptacle 652 configured to receive the tip of apusher tool that is used during implantation. As explained above inconnection with FIG. 5A, one or more pusher cups may be provided invarious locations.

FIG. 6B illustrates the LIMD 600 of FIG. 6A during installation, whilelocated within an introducer 660. The introducer has a distal end 662that is open to permit the LIMD 600 to be implanted and deployed therethrough. The introducer 660 includes a proximal end 664 along which apusher or other form of tool (e.g. a stylet) is used guide the LIMD 600into position. As shown in FIG. 6B, the stabilizer arm 630 and appendagearm 620 are contracted in their collapsed position to define an outerenvelope substantially no greater than the outer envelope of the body608 of the LIMD 600. The pusher device 662 may engage one or both of thepusher receptacle 640 in the pusher cup 634 and/or the pusher receptacle652 and the pusher cup 650. During implantation, the pusher or stylet662 is securely attached at the receptacle cup 634 to guide the LIMD 600to its activation site. Once the electrode 612 is located against thedesired tissue at the activation site, the pusher or stylet 662 may thenbe rotated to similarly cause the LIMD 600 and electrode 612 to rotateuntil securely affixed within the select tissue. As one example, thereceptacle 640 and/or receptacle 652 may have a noncircular crosssection as viewed from the top down (e.g. a rectangular triangle,hexagon, or other polygon shape) such that when the pusher or stylet 662is rotated, it remains securely fixed within the receptacle 640 toinduce rotation at the electrode 612.

FIGS. 7A and 7B illustrate an alternative embodiment for an LIMD 700when in the collapsed installation configuration (FIG. 7A) and in thedeployed flared position (FIG. 7B). The LIMD 700 includes a stabilizerarm 730 having a distal and proximal end 732, 736. An appendage arm 720is integrally formed, with and extends outward at an intermediateposition from, the stabilizer arm 730. The appendage arm 720 includes aproximal end 726 that is joined to the stabilizer arm 730 at anintermediate position away from the body 702 of the LIMD 700. Theappendage arm 720 includes an electrode 724 on the distal end thereof.As shown in FIG. 7A, before deployment and while in the collapsedposition, the appendage arm 720 does still slightly project outwardbeyond the outer envelope of the body 702, but the stabilizer arm 730extends along the direction substantially parallel to the longitudinalaxis of the body 702. In the example of FIG. 7A, the pusher cup 750 islocated at the distal top end of the body 702. The stabilizer arm 730has a hollow passage there through that receives a tool 762 that pushesthe LIMD 700 to a desired deployed position. For example, the passagethrough the stabilizer arm 730 aligns with the pusher cup 750 in thedistal top end such that the tool 762 is inserted into the passage untilsecurely engaging the pusher cup 750. When in the passage, the tool 762maintains the stabilizer arm 730 in a straight, elongated shapeextending along the longitudinal axis of the tool 762.

Turning to FIG. 7B, once the LIMD 700 is implanted and the introducerand tool 762 removed, the stabilizer arm 730 and appendage arm 720 arepermitted to flare outward to form a Y-shaped configuration. It shouldbe recognized that the shape formed by the stabilizer arm 730 andappendage arm 720 after deployment may be modified and controlled duringconstruction to achieve a desired final configuration when implanted. Byremoving the tool 762, the stabilizer arm 730 is permitted to return toits natural pre-formed shape.

FIG. 5C illustrates the LIMD 500 in an exemplary deployed position. Whendeployed as illustrated in FIG. 5C, the LIMD 500 may be located directlyagainst the ventricular vestibule. The electrode 512 is secured to theventricular vestibule and/or extended to a point such that the distalend of the electrode 512 projects into or is located directly againstthe surface tissue of the right ventricle. The appendage arm 520 isflared to its deployed position to locate the electrode 524 againstatrial tissue in the atrial appendage area. In the example of FIGS.5A-5C, the electrode 524 is configured to simply be pressed against thetissue at the atrial appendage. Optionally, spikes or a serrated edge orother fixation means may be added to the electrode at 524 to furtherfacilitate engagement to the tissue in the atrial appendage.

When deployed and in the flared position, the stabilizer arm 530 extendsinto the SVC and rests against the side of the SVC to providestabilization for the overall positioning of the LIMD 500. It should berecognized, that throughout operation, as the right atrium moves duringcontraction, the stabilizer arm 530 and appendage arm 520 constantlypivot, rotate and/or flex to avoid interference with the normalmechanical movement of the right atrium.

FIG. 6C illustrates an exemplary deployment of the LIMD 600 when locatedin the right atrium. The electrode 612 is securely affixed through theventricular vestibule and/or locate the distal end thereof within orimmediately adjacent the surface of the right ventricular wall. Theappendage arm 620 is flared to a deployed position to locate theelectrode 624 in the atrial appendage. The stabilizer arm 630 is alsoflared in the opposite direction to its deployed position such that thedistal end 632 extends into and engages tissue within the SVC. Asexplained above, the appendage arm 620 and stabilizer arm 630 areflexible and will constantly move in connection with the mechanicalcontraction of the right atrium to avoid interference with the normalmechanical movement of the heart.

As shown in FIGS. 5A-5C, 6A-6C, and 7A-7B, the LIMD may be provided withtwo or more fixation mechanisms at the top end of the device body. Onefixation mechanism, which is not electrically active, acts as tostabilize and passively-fixate the LIMD 300 in the superior vena cava(SVC). The other fixation mechanism is shorter but has an electrode atits tip and has the dual role of passive fixation to the RA appendageand pacing and sensing the RA. Additionally, the LIMD 300 has two ormore possible configurations for attachment to the implant (and possiblyexplant) tool at either the end of the SVC stabilization fixationmechanism or at the side of the LIMD body. When the LIMD is affixed tothe desired target site and the introducer (which protects blood vesselsand myocardium from being damaged by the helical cathode) is removed,the passive fixation mechanisms swivel away from the longitudinal axisof the LIMD and contact their respective sites. The degree by whichthese fixation mechanisms swivel away from each other may bepre-determined or controlled by a ratcheting mechanism via the implanttool. Alternatively, the LIMD may use a stylet after affixation to thetarget site, which transmutes the morphology of the fixation mechanismsfrom a “J-shape” to a “U-shape,” as shown in FIG. 7B.

In FIGS. 5C and 6C, the LLPM is affixed to the target site on theatrioventricular wall and is deployed in the RA. Here, it can be seenthat there are three points of contact between the LIMD and myocardium,significantly reducing the possibility of dislodgement. In addition,dual chamber (e.g. DDD or DDDR mode) functionality is achieved via theRA appendage fixation mechanism (which paces and senses the RA) and thehelical cathode electrode (which paces and senses the RV).

If dual-chamber pacing and sensing is achieved with a long helicalfixation electrode covered proximally with insulation, it may bedesirable to know when the helix has extended through the myocardium tothe adjacent chamber. This may be determined using real-time impedancemeasurement between the helical tip electrode and another electrode.When the helical electrode is in pooled blood of any heart chamber,characteristic low impedance will be between it and any other electrodein the blood. As the helical electrode is screwed into the myocardium,impedance will rise. When the helix has been affixed sufficiently tobreak through the wall to the other chamber, impedance will drop. Thechanges in impedance may be used to know how far to screw in the helix,which portions of walls delineating heart chambers are an appropriatethickness for the helix, and whether any other spacer is needed toprevent the device from torqueing with the heart's mechanical motion.

Before disconnecting from the insertion tool, a pacing test provides anindication of the chamber paced and capture threshold. If the test showsthat pacing is not occurring in the desired chamber or that thresholdsare inappropriate, the tool may be used to remove the fixation andattempt to attach at another location.

For each attempt, the distance traversed by the lead's AV helix throughthe wall between the RA and RV between each turn of the screw may beclosely controlled. Atrial and ventricular capture thresholds may berecorded with a pacing system analyzer (PSA) between each turn or at setdegrees of rotation. The PSA may use the electrodes on the LIMD or mayuse electrodes on the exterior or outer end of the introducer to testfor capture thresholds prior to affixing the LIMD in place. The distancebetween each turn may be generally between 0.5 to 2.0 mm. For example,all lead helical electrodes may be coated with an insulating materialsuch as Parylene®-coated except for the most distal portion of the pitchof the screws (thus ensuring that only tissue near the tip isstimulated). For example, the helical electrode may be advanced in smallincrements, and after each increment, the PSA may then test for acapture. An interactive process may be repeated whereby the electrode isadvanced and then the PSA determines if a capture threshold has beensatisfied. This process is repeated until impulses from the distalelectrode capture the ventricular tissue. Similarly, a capture test maybe performed for the atrial electrode. The atrial electrode is adjusteduntil the PSA confirms atrial capture. In accordance with the foregoing,it is possible for an AV helical electrode on a lead to burrow from theRA and excite ventricular tissue. This allows a dual chambermode-capable LIMD to have its main body located in the one chamber andpace and sense another chamber.

The term “distal” as used to describe wall tissue and activation sites,is used with respect to the local chamber.

FIG. 8 shows an exemplary LIMD 800 configured for dual-chamberfunctionality from a primary location within a single chamber of theheart. For example, the LIMD 800 may be implemented as a pacemaker,equipped with both atrial and ventricular sensing and pacing circuitry.Alternatively, the LIMD 800 may be implemented with a reduced set offunctions and components. For instance, the LIMD 800 may be implementedwithout ventricular sensing and pacing. The LIMD 800 may also beimplemented with an increased set of functions. For example, if the LIMD800 includes a coil type electrode, the LIMD may be configured toinclude cardioversion and/or shocking therapy capability.

The LIMD 800 has a housing 801 to hold the electronic/computingcomponents. The housing 801 (which is often referred to as the “can”,“case”, “encasing”, or “case electrode”) may be programmably selected toact as the return electrode for certain stimulus modes. Housing 801further includes a plurality of terminals 802, 804, 806, 808, 810 thatinterface with electrodes of the LIMD. For example, the terminals mayinclude: a terminal 802 that connects with a first electrode associatedwith the housing (e.g. electrode 410) and located in a first chamber; aterminal 804 that connects with a second electrode associated with thehousing (e.g., electrode 411) and also located in the first chamber; aterminal 806 that connects with a third electrode associated with thehousing (e.g. electrode 412) and located in the first chamber andpossibly partially extending into tissue associated with a secondchamber; and two additional terminals 808, 810 that connect with one ormore additional electrodes (e.g., electrode 524), if available. The typeand location of each electrode may vary. For example, the electrodes mayinclude various combinations of ring, tip, coil and shocking electrodesand the like.

The LIMD 800 includes a programmable microcontroller 820 that controlsvarious operations of the LIMD 800, including cardiac monitoring andstimulation therapy. Microcontroller 820 includes a microprocessor (orequivalent control circuitry), RAM and/or ROM memory, logic and timingcircuitry, state machine circuitry, and I/O circuitry.

LIMD 800 further includes a first chamber pulse generator 822 thatgenerates stimulation pulses for delivery by one or more electrodescoupled thereto. The pulse generator 822 is controlled by themicrocontroller 820 via control signal 824. The pulse generator 822 iscoupled to the select electrode(s) via an electrode configuration switch826, which includes multiple switches for connecting the desiredelectrodes to the appropriate I/O circuits, thereby facilitatingelectrode programmability. The switch 826 is controlled by a controlsignal 828 from the microcontroller 820.

In the example of FIG. 8, a single pulse generator 822 is illustrated.Optionally, the LIMD 800 may include multiple pulse generators, similarto pulse generator 822, where each pulse generator is coupled to one ormore electrodes and controlled by the microcontroller 820 to deliverselect stimulus pulse(s) to the corresponding one or more electrodes.

Microcontroller 820 is illustrated as including timing control circuitry832 to control the timing of the stimulation pulses (e.g., pacing rate,atrio-ventricular (AV) delay etc.). The timing control circuitry 832 mayalso be used for the timing of refractory periods, blanking intervals,noise detection windows, evoked response windows, alert intervals,marker channel timing, and so on. Microcontroller 820 also has anarrhythmia detector 834 for detecting arrhythmia conditions. Althoughnot shown, the microcontroller 820 may further include other dedicatedcircuitry and/or firmware/software components that assist in monitoringvarious conditions of the patient's heart and managing pacing therapies.

The LIMD 800 includes sensing circuitry 844 selectively coupled to oneor more electrodes through the switch 826. The sensing circuitry detectsthe presence of cardiac activity in the right chambers of the heart. Thesensing circuitry 844 may include dedicated sense amplifiers,multiplexed amplifiers, or shared amplifiers. It may further employ oneor more low power, precision amplifiers with programmable gain and/orautomatic gain control, bandpass filtering, and threshold detectioncircuit to selectively sense the cardiac signal of interest. Theautomatic gain control enables the unit 802 to sense low amplitudesignal characteristics of atrial fibrillation. Switch 826 determines thesensing polarity of the cardiac signal by selectively closing theappropriate switches. In this way, the clinician may program the sensingpolarity independent of the stimulation polarity.

The output of the sensing circuitry 844 is connected to themicrocontroller 820 which, in turn, triggers or inhibits the pulsegenerator 822 in response to the absence or presence of cardiacactivity. The sensing circuitry 844 receives a control signal 846 fromthe microcontroller 820 for purposes of controlling the gain, threshold,polarization charge removal circuitry (not shown), and the timing of anyblocking circuitry (not shown) coupled to the inputs of the sensingcircuitry.

In the example of FIG. 8, a single sensing circuit 844 is illustrated.Optionally, the LIMD 800 may include multiple sensing circuit, similarto sensing circuit 844, where each sensing circuit is coupled to one ormore electrodes and controlled by the microcontroller 820 to senseelectrical activity detected at the corresponding one or moreelectrodes. The sensing circuit 844 may operate in a unipolar sensingconfiguration or in a bipolar sensing configuration.

The LIMD 800 further includes an analog-to-digital (ND) data acquisitionsystem (DAS) 850 coupled to one or more electrodes via the switch 826 tosample cardiac signals across any pair of desired electrodes. The dataacquisition system 850 is configured to acquire intracardiac electrogramsignals, convert the raw analog data into digital data, and store thedigital data for later processing and/or telemetric transmission to anexternal device 854 (e.g., a programmer, local transceiver, or adiagnostic system analyzer). The data acquisition system 850 iscontrolled by a control signal 856 from the microcontroller 820.

The microcontroller 820 is coupled to a memory 860 by a suitabledata/address bus 862. The programmable operating parameters used by themicrocontroller 820 are stored in memory 860 and used to customize theoperation of the LIMD 800 to suit the needs of a particular patient.Such operating parameters define, for example, pacing pulse amplitude,pulse duration, electrode polarity, rate, sensitivity, automaticfeatures, arrhythmia detection criteria, and the amplitude, waveshapeand vector of each shocking pulse to be delivered to the patient's heart808 within each respective tier of therapy.

The operating parameters of the LIMD 800 may be non-invasivelyprogrammed into the memory 860 through a telemetry circuit 864 intelemetric communication via communication link 866 with the externaldevice 854. The telemetry circuit 864 allows intracardiac electrogramsand status information relating to the operation of the LIMD 800 (ascontained in the microcontroller 820 or memory 860) to be sent to theexternal device 854 through the established communication link 866.

The IMD 802 can further include magnet detection circuitry (not shown),coupled to the microcontroller 820, to detect when a magnet is placedover the unit. A magnet may be used by a clinician to perform varioustest functions of the unit 802 and/or to signal the microcontroller 820that the external programmer 854 is in place to receive or transmit datato the microcontroller 820 through the telemetry circuits 864.

The LIMD 800 may be equipped with a communication modem(modulator/demodulator) 840 to enable wireless communication with aremote device, such as a second implanted LIMD in a master/slavearrangement, such as described in U.S. Pat. No. 7,630,767. In oneimplementation, the communication modem 840 uses high frequencymodulation. As one example, the modem 840 transmits signals between apair of LIMD electrodes, such as between the can 800 and anyone of theelectrodes connected to terminals 802-810. The signals are transmittedin a high frequency range of approximately 20-80 kHz, as such signalstravel through the body tissue in fluids without stimulating the heartor being felt by the patient. The communication modem 840 may beimplemented in hardware as part of the microcontroller 820, or assoftware/firmware instructions programmed into and executed by themicrocontroller 820. Alternatively, the modem 840 may reside separatelyfrom the microcontroller as a standalone component.

The LIMD 800 can further include one or more physiologic sensors 870.Such sensors are commonly referred to as “rate-responsive” sensorsbecause they are typically used to adjust pacing stimulation ratesaccording to the exercise state of the patient. However, thephysiological sensor 870 may further be used to detect changes incardiac output, changes in the physiological condition of the heart, ordiurnal changes in activity (e.g., detecting sleep and wake states).Signals generated by the physiological sensors 870 are passed to themicrocontroller 820 for analysis. The microcontroller 820 responds byadjusting the various pacing parameters (such as rate, AV Delay, V-VDelay, etc.) at which the atrial and ventricular pacing pulses areadministered. While shown as being included within the unit 802, thephysiologic sensor(s) 870 may be external to the unit 802, yet still beimplanted within or carried by the patient. Examples of physiologicsensors might include sensors that, for example, sense respiration rate,pH of blood, ventricular gradient, activity, position/posture,temperature, minute ventilation (MV), and so forth.

A battery 872 provides operating power to all of the components in theLIMD 800. The battery 872 is capable of operating at low current drainsfor long periods of time, and is capable of providing high-currentpulses (for capacitor charging) when the patient requires a shock pulse(e.g., in excess of 2 A, at voltages above 2 V, for periods of 10seconds or more). The battery 872 also desirably has a predictabledischarge characteristic so that elective replacement time can bedetected. As one example, the unit 802 employs lithium/silver vanadiumoxide batteries.

The LIMD 800 further includes an impedance measuring circuit 874, whichcan be used for many things, including: impedance surveillance duringthe acute and chronic phases for proper LIMD positioning ordislodgement; detecting operable electrodes and automatically switchingto an operable pair if dislodgement occurs; measuring respiration orminute ventilation; measuring thoracic impedance; detecting when thedevice has been implanted; measuring stroke volume; and detecting theopening of heart valves; and so forth. The impedance measuring circuit874 is coupled to the switch 826 so that any desired electrode may beused.

The microcontroller 820 further controls a shocking circuit 880 by wayof a control signal 882. The shocking circuit 880 generates shockingpulses of low (e.g., up to 0.5 joules), moderate (e.g., 0.5-10 joules),or high energy (e.g., 811 to 40 joules), as controlled by themicrocontroller 820. Such shocking pulses are applied to the patient'sheart 808 through shocking electrodes, if available on the LIMD. It isnoted that the shock therapy circuitry is optional and may not beimplemented in the LIMD, as the various LIMDs described above andfurther below will typically not be configured to deliver high voltageshock pulses. On the other hand, it should be recognized that an LIMDmay be used within a system that includes backup shock capabilities, andhence such shock therapy circuitry may be included in the LIMD.

FIG. 9A provides a sectional view of a patient's heart 33 and shows anLIMD 900. The LIMD 900 may have been placed through the superior venacava 28 into the right atrium 30 of the heart 33. The LIMD 900 comprisesa housing 902 configured to be implanted entirely within a single localchamber of the heart. The housing 902 includes a proximal base end 904and a distal top end 906. The proximal base end 904 includes an activefixation member, such as a helix, that is illustrated to be implanted inthe ventricular vestibule (VV). A shaped intra-cardiac (IC) deviceextension 903 extends from the distal top end 906 of the housing 902.The IC device extension 903 comprises an elongated body that may betubular in shape and may include a metal braid provided along at least aportion of the length therein (as explained herein in more detail). Theextension body including a transition sub-segment, an activeinterim-segment and a stabilizer end-segment, all of which areillustrated in a deployed configuration and some of which are preloadedagainst anatomical portions of tissue of interest. For example, theactive interim-segment (e.g., second curved segment 911, and all orportions of the first and second linear regions 909 and 913) and thestabilizer end-segment (e.g., third curved segment 915 and all orportions of the second linear region 913) are shown preloaded againstanatomical tissue of interest. The braid resists torque compression butpermits lateral flex. One or more electrodes 905 are carried by the ICdevice extension 903 and are electrically connected to electronicswithin the housing 902 through conductors extending through the body ofthe IC device extension.

The IC device extension 903 is formed with shape memory characteristicsthat allow the IC device extension 903 to transform between a collapsedstate, in which the IC device extension assumes a substantially linearshape, and an expanded state, in which the IC device extension assumes amultiple curved shape, such as shown in FIGS. 9A-9D. In one embodiment,the curved configuration of the IC device extension 903 comprisesmultiple sharply curved segments, obtusely curved segments, generallylinear regions and the like. The number, length, and order of thesegments and regions, as well as the degree to which individual segmentsor regions are curved or linear may vary depending upon the anatomicalcontour to be followed.

The IC device extension includes a short stem 930 that extends a shortdistance from the distal top end 906 of the housing 902. The stem 930merges into a first curved segment 907 that turns at a sharp angle withrespect to a longitudinal axis of the housing 902. Optionally, the firstcurved segment 907 may form an acute angle, 90 degree angle, or obtuseangle approximately with respect to a longitudinal axis of the housing902. The first curved segment 907 merges into and is followed by a firstgenerally linear region 909 that extends laterally from the housing 902,along a lateral axis, until merging with a second curved segment 911.The second curved segment 911 turns at a sharp angle with respect to thelongitudinal axis of the housing 902 and the lateral axis of the firstlinear region 909. Optionally, the second curved segment 911 may form anacute angle, 90 degree angle, or obtuse angle approximately with respectto the lateral axis of the first linear region 909. As one example, thesecond curved segment 911 may approximate a 180 degree sharp or“hairpin” curve away from the lateral axis of the first linear region909 and away from the longitudinal axis of the housing 902. The secondcurved segment 911 merges into and is followed by a second generallylinear region 913 that extends along a second lateral direction.

One or more electrodes 905 are located along the second curved segment911. Optionally, the electrode(s) may be provided in the regionproximate to the junction of the second curved segment 911 and thesecond linear region 913. Optionally, one or more electrodes 905 may beprovided along the second linear region 913.

The second linear region 913 merges with and extends to a third curvedsegment 915. The third curved segment 915 follows an extending “slow”arc and then terminates at a tail end 917 of the IC device extension903. The third curved segment 915 follows a slow arc with respect to thelongitudinal axis of the housing 902 and the lateral axis of the firstlinear region 909. As one example, the third curved segment 915 mayapproximate a 90 degree turn away from the longitudinal axis of thehousing 902 until terminating at the tail end 917 of the IC deviceextension 902.

The shaped IC device extension 903 is formed into a pre-loaded shape inwhich the first, second and third curved segments 907, 911 and 915extend along desired arcuate paths and project from longitudinal/lateralaxes at desired pitch, roll and yaw angles, where the pitch, roll andyaw angles are measured from reference angular positions. To avoidoverly complicating FIG. 9A, examples of longitudinal/lateral axis,arcuate paths, pitch, roll and yaw angles are shown in the embodiment ofFIG. 9E, but are equally applicable to any other embodiments describedherein.

With continued reference to FIG. 9A, the LIMD 900 is configured to placethe housing 902 in the lower region of the right atrium between the OSand IVC with a distal helix electrode, on the housing 902, in theventricular vestibule to provide ventricular pacing and sensing. The ICdevice extension 903 extends upward in the right atrium toward and intothe SVC. The IC device extension 903 is configured (length wise andshape wise) such that the second curved segment 911 may be implantedwithin the right atrial IC device extension (RAA), along with thoseportions of the first and second linear regions 909, 913 near the secondcurved segment 911. The configuration in FIG. 9A places the electrode905 in the RAA to allow for right atrial pacing and sensing. Theconfiguration in FIG. 9A also places the proximal portion of the thirdcurved segment 915 against a wall of the SVC to provide overallstability to the LIMD 900.

FIG. 9B illustrates a model of an interior of a canine heart and shows aleadless implantable medical device having a shaped IC device extensionsimilar to that describe with reference to FIG. 9A. The embodiments ofFIGS. 9A and 9B may have IC device extensions that traverse atwo-dimensional space, i.e., lie substantially flat in a plane, whileextending in x and y directions along its length, or a three-dimensionalspace, i.e., extending in x, y and z directions along its length.

FIGS. 9C and 9D further illustrate a model of an interior of a humanheart and shows an example of the LIMD 900 having the shaped IC deviceextension 903 described with reference to FIG. 9A. FIG. 9C generallyillustrates an exemplary right lateral view of a heart, while FIG. 9Dgenerally illustrates an exemplary anterior-posterior (AP) view. Aspoints of reference, the RV vestibule 920, atrial IC device extension924, and RV outflow track 922 are illustrated in one or both of FIGS. 9Cand 9D. The AP view of FIG. 9D is oriented relative to the right lateralview of FIG. 9D, such that the viewer's line of sight (in FIG. 9D) isdirected into the atrial IC device extension 924 along arrow 926 in FIG.9C, whereas the viewer's line of sight in FIG. 9C is directed in thedirection of arrow 928 in FIG. 9D.

The LIMD 900 is shown to be actively affixed near the RV vestibule 920.The views illustrated in FIGS. 9C and 9D are merely exemplary models ofa potential three dimensional shape of the IC device extension 903. Tofurther illustrate the 3D geometry of the IC device extension 903,planes 932-934 are shown in dashed line. The plane 932 generally followsX and Y axes that are defined with respect to the orientation of thehousing 902. For example, the Y axis may correspond to the longitudinalaxis of the housing 902. The plane 933 generally follows X and Z axes,wherein the X axis is oriented laterally with respect to thelongitudinal axis of the housing 902 (e.g., from left to right acrossthe drawing sheet). The Z axis is oriented transversely with respect tothe longitudinal axis of the housing 902 and the lateral X axis (e.g.,in and out of the drawing sheet).

The plane 932 (also referred to as the LIMD plane) is generally definedby the longitudinal axis of the housing 902, and a lateral axis alongwhich the first linear region 909 extends. The plane 933 (also referredto as the RAA plane) is generally defined by the lateral axis alongwhich the first linear region 909 extends and the transverse axis alongwhich the second linear region 913 extends. The plane 934 (also referredto as the stabilization or SVC plane) is generally defined by thetransverse axis along which the second linear region 913 extends and astabilization path along which the third curved region 915 extends.

FIG. 9E provides an enlarged view of a portion of a shaped IC deviceextension 953, while in the right atrial IC device extension 974,accordance with an alternative embodiment. The shaped IC deviceextension 953 includes a short stem 980 that extends a short distancefrom the distal top end 906 of the housing 952 of an LIMD. The stem 980merges into a first curved segment 957 that turns at a sharp angle withrespect to a longitudinal axis 942 of the housing 902. Optionally, thefirst curved segment 957 may form an acute angle, a 90 degree angle, oran obtuse angle approximately with respect to the longitudinal axis 942of the housing 952. The first curved segment 957 merges into and isfollowed by a first generally linear region 959 that extends laterallyfrom the housing 902, along a lateral axis 943, until merging with asecond curved segment 961. The second curved segment 961 turns at acompound sharp angle with respect to the longitudinal axis 942 of thehousing 952 and the lateral axis 943 of the first linear region 959.Optionally, the second curved segment 961 may form an acute angle, a 90degree angle, or an obtuse angle approximately with respect to thelateral axis 943 of the first linear region 959. As one example, thesecond curved segment 961 may approximate a 180 degree sharp or“hairpin” curve away from the lateral axis 943 of the first linearregion 959 and away from the longitudinal axis 942 of the housing 952.The second curved segment 961 merges into, and is followed by, a secondgenerally linear region 963 that extends along a second lateraldirection 944.

One or more electrodes 955 are located along the second curved segment961. Optionally, the electrode(s) 955 may be provided in the regionproximate to the junction 951 of the second curved segment 961 and thesecond linear region 963. Optionally, one or more electrodes 955 may beprovided along the second linear region 963. The electrode 955 includesa bracket ring 956 that at least partially surrounds the perimeter ofthe body of the shaped IC device extension 903. The bracket ring 956 isformed with a spring arm 957 that includes an outer bend 958 thatterminates at a distal tip 959.

The second curved segment 961 follows an arcuate path 947, while thespring arm 957 extends outward from the arcuate path 947 in a tangentialdirection 946 to form an acute angle with the second lateral axis 944.The distal tip 959 may be directed inward toward the second linearregion 963 such as to avoid damaging wall tissue. The spring arm 957pivots, relative to the second curved segment 961 and relative to thesecond linear segment 963, inward and outward along arrow 948 and 949.The spring arm 957 is biased outward in the direction of arrow 949 to anormal resting position. When implanted, the tissue wall places a loadagainst, and slightly deflects, the spring arm 957 inward along arrow948, thereby affording constant and steady contact between the electrode955 and the tissue wall in the right atrial IC device extension 974.

The second linear region 963 merges with and extends to a third curvedsegment 965. The third curved segment 965 follows an extending “slow”arc and then terminates at a tail end of the IC device extension 953.The third curved segment 965 follows a slow arc, along an arcuate path945, with respect to the longitudinal axis 942 of the housing 952 andthe first and second lateral axes 943 and 944 of the first and secondlinear regions 959 and 963.

The lateral axis 943 of the first linear region 959 projects from thelongitudinal axis 942 at a yaw angle 975, where the yaw angle 975 ismeasured from a zero reference yaw angle about the longitudinal axis942. The second curved segment 974 bends in a direction that projectsfrom, or about, the lateral axis 943, at a roll angle 976, where theroll angle 976 is measured from a zero reference roll angle about thelateral axis 943. The second linear region 963 extends along the secondlateral axis 944 at a complex angle with respect to the lateral axis943. The third curved segment 965 projects from the second lateral axis944, at a pitch angle 977 from a zero reference pitch angle about thesecond lateral axis 944.

It should be understood that the axes, directions, curves, and linearpaths followed by the regions and segments of the shaped IC deviceextension 903 of FIG. 9A may resemble or differ from the axes,directions, curves, and linear pathes followed by the regions andsegments of the shaped IC device extension 953 of FIG. 9E.

FIG. 9F illustrates a longitudinal axial view of an introducer assembly280, formed according to an embodiment with the LIMD 900 including theIC device extension 903 of FIG. 9A inserted therein. The IC deviceextension 903 includes an extension body having a proximal end 353. Theintroducer assembly 280 includes a flexible, longitudinal, cylindricalopen-ended sheath 282 defining a central internal passage 284. Thesheath 282 may be a flexible tube formed of rubber, for example, that isconfigured to be maneuvered through patient anatomy, such as veins andthe heart. In this respect, the sheath 282 may be similar to that of acardiac catheter.

A physician or surgeon operates user controls on the introducer assembly280 at a proximal end (not shown). The proximal end may include usercontrols that allow the sheath 282 to be bent, curved, canted, rotated,twisted, or the like, so as to be navigated through a patient'svasculature. For example, a distal end 288 of the sheath 282 may bebent, curved, canted, rotated, twisted, articulated, or the like throughoperation by the physician or surgeon manipulating the user controls atthe proximal end of the assembly 280.

The LIMD 900 is held in the distal end 288 of the sheath 282. As shown,the housing 902 of the LIMD 900 slides along inner walls 292 of thesheath 282. The LIMD 900 is configured to be pushed out of, or ejectedfrom, the sheath 282 in the direction of arrow A. The top end 906 of theLIMD 900 connects to the IC device extension 903. The proximal end 353of the IC device extension 903 is coupled to the housing 902 of the LIMD900. The extension body extends between the proximal end 353 and adistal end 355. The extension body including a transition sub-segment357, an active interim-segment 360 and a stabilizer end-segment 362, allof which are “stretched out” or elongated to extend generally along thelength of the internal passage 284 of the sheath 282.

With cross-reference to FIGS. 9A-9E, the transition sub-segment 357generally includes the stem 930, first curved segment 907 and at least aportion of the first linear region 909. The active interim-segment 360includes the second curved segment 911, and may include portions of thefirst and second linear regions 909 and 913. The stabilizer end-segment362 includes the third curved segment 915 and may include a portion ofthe second linear region 913. It should be recognized that thecorrelation between the segments and regions of FIGS. 9A-9E and thetransition sub-segment 357, active interim-segment 360 and stabilizerend-segment 362, are exemplary implementations. Similarly, thetransition sub-segment 357, active interim-segment 360 and stabilizerend-segment 362 may be correlated to the stabilization arms andappendage arms described in connection with the embodiments of FIGS.5-7.

The extension body is formed of materials that are flexible, yet offergood shape memory such that the extension body may be stretched outwhile within the sheath 282 and, when removed from the sheath 282, thenreturn to its original (normal, resting) shape as shown in FIG. 1A. Forexample, the extension body may be formed of silicon that is cured todesired crosslink structure that holds (or is biased to return to) apre-loaded shape (e.g., through a thermal set process).

In the example shown in FIG. 9F, the active interim-segment 360 (e.g.,corresponding to second curved segment 911) is straightened to removethe curved shape only while in the sheath 282. Similarly, the stabilizerend-segment 362 (e.g., corresponding to the third curved segment 915) isstraightened. While the example of FIG. 9F illustrates a slight wave orcurve that remains in the extension body, optionally, the extension bodymay be constrained to be much straighter or permitted to remain evenmore curved or bent. The amount to which the active interim-segment 360and stabilizer end-segment 362 are straightened or curved may varydepending upon the outer dimensions of the extension body and the innerdimensions of the sheath 282.

A pusher rod 296 is provided to be slidably inserted into the sheath 282in order to manipulate the IC device extension 903 and LIMD 900. Forexample, the pusher rod 296 may linearly translate the IC deviceextension 903 and LIMD 900 along the longitudinal axis 283 and rotatethe IC device extension 903 and LIMD 900 about the rotational axis 285.The pusher rod 296 includes a pusher tip connector 298 that isconfigured to securely engage the distal end 355 of the extension body.The distal tip 355 includes a connection member 394 that is configuredto securely mate with the pusher tip connector 298 (e.g., through athreaded connection, an interference fit, or the like). The pusher rod296 may extend into and retract from the sheath 282 under a physician'scontrol. The pusher rod 296 and LIMD 900 are located at opposite ends ofthe extension body. However, rotational force applied by the pusher rod296 on the distal end 355 of the extension body is substantially alltransferred to the LIMD 900. This rotational force may be used toactively secure the LIMD 900 to the wall tissue through the activefixation member, such as a helical anchor, a coil, a helical wire havinga sharp point, a hook, a barb, or the like.

FIG. 9F also illustrates the general internal components of the LIMD900. The housing 902 include a charge storage unit 324 and a battery 326that supplies power to the electronics and energy to the charge storageunit 324. The housing 302 also includes a sensing circuit 322 and acontroller 320.

The sensing circuit 322 senses intrinsic activity, while the changestorage unit 324 stores high or low energy amounts to be delivered inone or more stimulus pulses. Electrodes 311, 905 may be used to deliverlower energy or high energy stimulus pulses, such as pacing pulses,cardioverter pulse trains, defibrillation shocks and the like. Theelectrodes 311, 905 may also be used to sense electrical activity, suchas physiologic and pathologic behavior and events and provide sensedsignals to the sensing circuit 322. The electrodes 311, 905 areconfigured to be joined to an energy source, such as the charge storageunit 324. The electrodes 311, 905 receive stimulus pulse(s) from thecharge storage unit 324. The electrodes 311, 905 may be the same ordifferent size.

The controller 320, within the housing 302, controls the overallfunctionality of the LIMD 900 including causing the charge storage unit324 to deliver activation pulses through each of the electrodes 311, 905in a synchronous manner, based on information from the sensing circuit322, such that activation pulses delivered from the electrode 311 aretimed to initiate activation in the adjacent chamber, while activationpulses delivered from the electrodes 905 are timed to initiateactivation in the local chamber. The stimulus pulses are deliveredsynchronously to local and distal activation sites in the local anddistal conduction networks such that stimulus pulses delivered at thedistal activation site are timed to cause contraction of the adjacentchamber in a predetermined relation to contraction of the local chamber.The electrodes 311, 905 are spaced radially and longitudinally apartfrom one another such that the local activation site (e.g., rightatrium) and the distal activation side in the adjacent chamber (e.g.,right ventricle) are sufficiently distant from one another within theheart's conductive network to initiate activation in different branchesof the hearts conductive network in a time relation that corresponds tothe normal hemodynamic timers (e.g. AV delay).

The controller 320 may operate the LIMD 900 in various modes asdiscussed herein. The sensing circuit 322 receives sensed signals fromone or more of the electrodes 311, 905. When pairs of electrodes areprovided in the location of electrode 311 or in the location ofelectrode 905, the sensing circuit 322 discriminates between sensedsignals from respective pairs of electrodes that originate in the nearfield and in the far field. For example, a pair of electrodes 905 maysense electrical potential across small areas and thereby allow thesensing circuit 322 to discriminate between different sources ofelectrical signals. In one embodiment, the inter-electrode gap 370between electrodes 905 is limited or minimized in order to achieve aselect type of sensing such as bipolar sensing which limits or minimizessensing of far field signals. With a small inter-electrode gap orseparation 370, when far field signals (e.g., signals from the rightventricle, left atrium or left ventricle) reach the electrodes 905 thesefar field signals are sensed as a common mode signal with no or a verysmall potential difference between the electrodes. Similarly, if a pairof electrodes 311 are provided on the active fixation member 310, theelectrodes 311 may be separated by a small inter-electrode gap suchthat, when far field signals (e.g., signals from the right atrium orleft ventricle) reach the electrodes 311 these far field signals aresensed as a common mode signal with no or a very small potentialdifference between the electrodes.

Optionally, an electrode 312 may be provided on the housing 302 andoperate as an anode electrode, while the electrode 311 and/or electrodes905 may operate as cathode electrodes. When an anode electrode 312 isprovided on the housing 302, the controller 320 may be configured tocause stimulus pulses to be delivered between the anode electrode 312and the first electrode 311 to stimulate the local chamber. When ananode electrode 312 is provided on the housing 302, the sensing circuit312 may be configured to sense between the anode 312 and the secondelectrode 905 or 311.

FIG. 9G illustrates a cross section of a portion of the IC deviceextension of FIGS. 9A-9E. Optionally, FIG. 9G may also represent thecross section of the appendage arm of FIGS. 5A to 7B or thestabilization arm of FIGS. 5A to 7B but with the electrodes andinsulated conductors removed. The IC device extension 360 includes oneor more insulated conductors 376 that are connected to correspondingelectrodes 368. The conductors 376 are connected through a switch toelectronics within the LIMD 900 to perform sensing and/or deliverstimulus pulses. The conductors 376 may be wound about one another in ahelical manner. The conductors 376 extend along a core 378 and theconductors 376 are radially surrounded by an elongated braid 380. Thebraid 380 may be made of steel or wire mesh, or have a honeycomb patternthat resists compression or IC device extension along the length of theIC device extension body (as denoted by longitudinal direction 386). Thebraid 380 is flexible in a lateral direction 388 in order to be bentside to side during implant and following implant. The mesh or honeycombconfiguration of the braid 380 affords strong resistance to torque aboutthe length of the IC device extension body when turned in the rotationaldirection 390 about the longitudinal direction 386. It is desirable tobe resistant to torque in order that, during implant, when a rotationalforce is applied to one end of the IC device extension body,substantially all of such rotational force is conveyed along the lengthof the IC device extension body to the opposite end. As explainedhereafter, the braid 380 facilitates delivery of rotational forces andlongitudinal pressure to the LIMD 900 and the active fixation memberduring implant.

Optionally, the IC device extension body may further includes aninsulation material 382 provided around the conductors 376 and aroundthe braid 380. An insulated, flexible, biocompatible shell 384 is formedover the braid 380. The electrodes 368 are connected to separatecorresponding conductors 376 at contacts 392. The electrodes 368 may beformed as ring electrodes, coil electrodes, pin or bump electrodes andthe like. While two electrodes 368 are illustrated it is understood thatonly one or more than two electrodes 368 may be provided on the ICdevice extension body. The electrodes 368 may be provided at variouspoints about the perimeter of the IC device extension body and atmultiple points along the length of the IC device extension body.

The electrodes 368 are separated from the braid 380 by insulation (e.g.part of the shell 384). The electrodes 368, braid 380 and conductors 376may be arranged concentrically with one another in a coaxiallyconfiguration.

FIG. 10 illustrates a LIMD 1000, according to an embodiment. The LIMDincludes a housing 1002 having a heart-wall securing base 1004 and a topor proximal end 1006. An anchoring member, such as a securing helix1008, which may be formed of a conductive material, such as metal,extends from the base 1004 of the housing 1002 and is configured tosecurely anchor the housing 1002, and therefore the LIMD 1000, to tissuewithin a chamber of a heart. The securing helix 1008 may also serve asan electrode. Instead of the securing helix 1008, a barb, hook, or thelike may extend from the housing 1002. Additionally, the anchoringmember may be any of the securing configurations shown in FIGS. 4A-G.

The proximal end 1006 of the housing 1002 connects to a stabilizing ICdevice extension 1010 having a stabilizing loop member. The stabilizingloop member of the stabilizing IC device extension 1010 may include alinear beam 1012 that connects to a first or inner loop 1014 that, inturn, connects to a second or outer loop 1016. The outer loop 1016 isdistally located from the housing 1002. Alternatively, the IC deviceextension 1010 may not include the linear beam 1012, but instead mayinclude just the loops 1014 and 1016 that join directly to the housing1002. Additionally, more or fewer loops than shown may be used. Forexample, the LIMD 1000 may include only one loop, or the LIMD 1000 mayinclude three or more loops.

The inner and outer loops 1014 and 1016 each have a perimeter that maybe flared (for example, diverges and then re-merges) in a directiongenerally toward and away from the lateral axis X which extends in alateral direction with respect to the longitudinal axis Y of the loops1014 and 1016 and housing 1002. The inner and outer loops 1014 and 106may have different contoured shapes, as shown in FIG. 10. By way ofexample, the loops 1014 and 1016 may have a perimeter, when viewed fromthe top down, that is disc-shaped, oval, circular, tubular, rectangular,triangular, and the like.

The loops 1014 and 1016 have opposed top and bottom sides that arealigned generally in parallel planes that extend in a generally commondirection as the longitudinal axis Y. The loops 1014 and 1016 arealigned along a common path. Alternatively, the loops 1014 and 1016 maybe oriented in a different manner with respect to one another. Forexample, the loops 1014 and 1016 may be oriented orthogonal to oneanother, such that the loop 1014 is oriented in a plane defined by the Xand Y axes, while the loop 1016 is oriented in a plane defined by the Yand Z axes, or vice versa. Moreover, it is recognized that, while FIG.10 illustrates the loops 1014 and 1016 aligned in a straight manner,this is for illustration purposes. When implanted, the loops 1014 and1016 will curve and wrap to follow the contour of an interior of theheart in a manner determined by the implanting physician. The loops 1014and 1016 are shown in FIG. 10 in a deployed implanted shape, but areflexible and are compressed into a collapsed installation shape whilebeing installed.

Electrodes 1018 are secured to the inner loop 1014 on either side andare configured to contact interior wall portions of the superior venacava of the heart. A radio marker 1020 may be secured next to anelectrode 1018. Although the electrodes 1018 are shown on the inner loop1014, the electrodes 1018 may be positioned on the outer loop 1016.Alternatively, each loop 1014 and 1016 may have one or more electrodes.

The electrodes 1018 are spaced apart from one another by aninter-electrode spacing (for example, the diameter of the loop segment1014). The electrodes 1018 may be wrapped around, or otherwise securedto, a peripheral portion of the inner loop 1014. As shown in FIG. 10,two electrodes 1018 are secured around circumferential portions of theinner loop 1018 at diametrically opposite sides 1022 and 1024.

The inner and outer loops 1014 and 1016 are joined to one another atconnection links or joints. As shown, the electrodes 1018 are distallylocated from one another on the inner loop 1014 and may be positionedgenerally at a radial angle θ that is 90° from the connection link orjoint with outer loop 1016, for example. The opposed electrodes 1018 areconfigured to contact tissue portions within a heart. The number ofelectrodes 1018 may vary depending on a particular application. Forexample, additional electrodes may be secured to the inner and/or outerloops 1014 and 1016. Additionally, while the electrodes 1018 are shownat opposite sides 1022 and 1024 of the inner loop 1014, the electrodes1018 may be positioned at various other locations on the inner loop1014, and even at different locations from the connection joint. Also,more or less electrodes 1018 than those shown on the inner loop 1014 maybe used. For example, the inner loop 1014 may include only one electrode1018.

The electrodes 1018 may be used to deliver low energy or high energystimulus, such as pacing pulses, cardioverter pulse trains,defibrillation shocks and the like. The electrodes 1018 may also be usedto sense electrical activity, such as physiologic and pathologicbehavior and events.

The dual-loop IC device extension 1010 includes shape memorycharacteristics that allow the inner and outer loops 1014 and 1016 totransform between collapsed states, in which the loops 1014 and 1016assume a substantially flat or compressed shape, and an expandeddeployed state, in which the loops 1014 and 1016 assume a more roundedloop shape. In an alternate configuration one or both of the loops mayhave an open configuration provided by a break in loop continuity alongthe perimeter of the loop.

The radio marker 1020 may be used to determine the position of the innerloop 1014 within patient anatomy. For example, the radio marker 1020 maybe used in conjunction with an electromagnetic surgical navigationsystem and an imaging device, such as a fluoroscope, to track theposition of the LIMD 1000 within patient anatomy. For example, afluoroscope may image the patient anatomy. The position of the radiomarker 1020 may then be registered with respect to the fluoroscopicimages. Thus, as the LIMD 1000 moves within the patient anatomy, adisplay showing the fluoroscopic image(s) and a representation of theLIMD 1000 may track movement of the LIMD 1000 through movement of theradio marker 1020, which was previously registered with the fluoroscopicimage(s).

While one radio marker 1020 is shown, more radio markers may be used.For example, radio markers may be secured to both loops 1014 and 1016and/or the linear beam 1012. Alternatively, the LIMD 1000 may notinclude a radio marker.

FIG. 11 illustrates an LIMD introducer assembly 1100, according to anembodiment. The introducer assembly 1100 includes a flexible tube,sheath, or the like 1102, such as a catheter, having an internallongitudinal passage 1104 into which the LIMD 1000, including the loops1014, 1016 and the housing 1002, are retained. The introducer assembly1100 is maneuvered by a physician at a proximal end (not shown) into aheart of a patient such that the housing 1002 is positioned in a lowerregion of the right atrium between the OS and IVC. The housing 1002 isanchored in place through the securing helix 1008.

As shown in FIG. 11, the inner and outer loops 1014 and 1016 of the LIMD1000 are collapsed or compressed within the flexible tube 1102 into acollapsed installation shape. This arrangement is designed to preventpremature deployment of the LIMD 1000 and prevent damage to vascularaccess ways for implantation. A pusher implant tool 1106 affixes to theproximal end 1006 of the housing 1002 and may use hooks or expandingcollets to lock into inner loop 1014. The introducer assembly 1100 isdesigned to be steerable so that the LIMD 1000 can be finely navigatedto the desired implant site.

Once the implantation site in the right atrium is located (viafluoroscopy, echocardiography, or other means), a distal end 1108 of theintroducer assembly 1100 is positioned at the implantation site and thepusher implant tool 1106 is pushed in the direction of arrow A to placethe securing helix 1008 adjacent tissue. The pusher implant tool 1106 isthen rotated in the direction of arc B. The rotation translates to thehousing 1002 and in turn to the securing helix 1008. The securing helix1008, which as noted above may also serve as an electrode, extends intothe myocardium through the right atrium, causing it to drill intoventricular tissue that bounds the right atrium. Then, the fidelity ofthe implantation process may be verified by ventricular capture andsensing tests.

Next, the introducer assembly 1100 is retracted enough to allow theinner loop 1014 to extend out of the sheath in the region of the highright atrium at the SVC/RA junction. The steerable introducer assembly1100 is adjusted to have the radio marker 1020 (shown in FIG. 10)located at the desired location and the inner loop 1014 in good contactwith atrial tissue.

Finally, the introducer assembly 1100 is further retracted relative tothe LIMD 1000 until the outer loop 1016 passes out of the tube 1102.That is, the introducer assembly 1100 is pulled back in the direction ofarrow A′, leaving the housing 1002 secured to the heart 12 within theright atrium. The introducer assembly 1100 disengages from the LIMD 1000as the introducer assembly 1100 is pulled away in the direction of arrowA′. Accordingly, the outer loop 1016 expands until it reaches the innerdiameter of the SVC. The pusher tool 1106 is then disengaged from thehousing 1002 and/or the first loop 1014.

FIG. 12 illustrates the LIMD 1000 implanted within a heart 1200 of apatient, according to an embodiment. The LIMD 1000 is implanted entirelywithin the heart 1200. The LIMD 1000 is configured to place the housing1002 in the lower region of the right atrium 1202 between the OS and theIVC 1204 with the securing helix 1008 in the ventricular vestibule 1206to provide ventricular pacing and sensing. The LIMD 1000 is furtherconfigured such that the dual-loop IC device extension 1010 extendsupward in the right atrium 1202 toward and into the SVC 1210. Thedual-loop IC device extension 1010 is configured (length-wise andshape-wise) such that the inner loop 1014 may be implanted in the upperregion of the right atrium 1202 near the junction of the right atrium1202 and the SVC 1210. As shown, the electrodes 1018 are compressed intoinner walls of the heart 1200 proximate the junction of the SVC 1210 andthe right atrium 1202. As such, the inner loop 1014 in the right atriumis configured for right atrial pacing and sensing. When in its expandedstate, the inner loop 1014 has an outer diameter greater than the innerdiameter of the SVC 1210.

As shown, the outer loop 1016 is secured within the heart 1200 such thatthe majority of the outer loop 1016 is positioned within the SVC 1210 toprovide passive mechanical stabilization of the LIMD 1000. When in itsexpanded state, the outer diameter of the outer loop 1016 is greaterthan the inner diameter of the SVC 1210.

FIG. 13 illustrates a LIMD 1300, according to an embodiment. The LIMD1300 is similar to the LIMD 1000 shown and described with respect toFIG. 10, except that the LIMD 1300 includes a stabilizing loop memberhaving a single loop 1302 connected to a housing 1304 through a linearbeam 1306. Alternatively, instead of using a linear beam, the singleloop 1302 may connect directly to the housing 1304. A securing helix1320 extends from a base of the housing 1304. Electrodes 1310 arepositioned on outer portions of the loop 1302, as discussed above, and aradio marker 1312 may also be positioned on the loop 1302. The singleloop 1302 anchors the LIMD 1300 within a local chamber of the heart,such as the right atrium.

FIG. 14 illustrates the LIMD 1300 implanted within a heart 1400 of apatient, according to an embodiment. The housing 1304 is containedwithin the right atrium 1402. The single loop 1302 is secured within theSVC 1404 such that the electrodes 1310 are compressed into inner wallsof the SVC 1404. The securing helix 1320 is anchored into the tissue ofthe right atrium 1402, as discussed above.

As shown in FIGS. 12 and 14, embodiments provide an LIMD that may becontained within the right atrium such that the housing is entirelywithin the right atrium and the IC device extension is passively securedwithin the SVC and/or a junction of the SVC and right atrium.Alternatively, the LIMD may be contained within any other local chamber.For example, the housing may be secured within the right ventricle,while the IC device extension is passively secured within the SVC and/ora junction of the SVC and right atrium.

As explained above, embodiments provide a LIMD that is compact andconfigured to be retained within a chamber of the heart. Embodimentsherein utilize an intra-cardiac implantable medical device havingsecuring IC device extension that is pre-formed into planar disc-shapedsegments, such as loops. The IC device extension is coupled to a housingof the LIMD. The LIMD is configured to be positioned within a localchamber of the heart, with the IC device extension extending into, andbeing passively anchored within, the SVC, for example. For example, thehousing of the LIMD may be completely contained within the right atriumof the heart.

Optionally, droplets or small amounts of a steroid may be added atselect points along the IC device extension and LIMD to promote tissuegrowth.

It is to be understood that the above description is intended to beillustrative, and not restrictive. For example, the above-describedembodiments (and/or aspects thereof) may be used in combination witheach other. In addition, many modifications may be made to adapt aparticular situation or material to the teachings of the inventionwithout departing from its scope. While the dimensions, types ofmaterials and coatings described herein are intended to define theparameters of the invention, they are by no means limiting and areexemplary embodiments. Many other embodiments will be apparent to thoseof skill in the art upon reviewing the above description. The scope ofthe invention should, therefore, be determined with reference to theappended claims, along with the full scope of equivalents to which suchclaims are entitled. In the appended claims, the terms “including” and“in which” are used as the plain-English equivalents of the respectiveterms “comprising” and “wherein.” Moreover, in the following claims, theterms “first,” “second,” and “third,” etc. are used merely as labels,and are not intended to impose numerical requirements on their objects.Further, the limitations of the following claims are not written inmeans—plus-function format and are not intended to be interpreted basedon 35 U.S.C. §112, sixth paragraph, unless and until such claimlimitations expressly use the phrase “means for” followed by a statementof function void of further structure.

What is claimed is:
 1. A leadless intra-cardiac medical deviceconfigured to be implanted entirely within a heart of a patient, thedevice comprising: a housing configured to be securely attached to aninterior wall portion of a chamber of the heart, the housing having aproximal end and a distal end, and the housing hermetically enclosingelectronics, a controller, and a battery; a securing device extendingfrom the proximal end of the housing, the securing device configured tosecure the housing to cardiac tissue; an appendage arm extending fromthe distal end of the housing, the appendage arm having a proximal enddirectly connected to the distal end of the housing, and the appendagearm having a distal end upon which an electrode is disposed; astabilizer arm extending from the distal end of the housing, thestabilizer arm having a proximal end directly connected to the distalend of the housing, and the stabilizer arm having a distal end uponwhich a pusher cup is disposed.
 2. The device of claim 1, wherein theappendage arm is rotatably connected to the distal end of the housing bya first hinge assembly, and wherein the stabilizer arm is rotatablyconnected to the distal end of the housing by a second hinge assembly.3. The device of claim 1, wherein the appendage arm is fixedly securedto the distal end of the housing, wherein a body of the appendage armcomprises a flexibly material having a desired preformed resting shapethat is non-linear, wherein the stabilizer arm is fixedly secured to thedistal end of the housing, and wherein a body of the stabilizer armcomprises a flexibly material having a desired preformed resting shapethat is non-linear.
 4. The device of claim 1, wherein the securingdevice is an active fixation helix.
 5. The device of claim 1, whereinthe appendage arm is rotatably connected to the distal end of thehousing by a first hinge assembly, and wherein the stabilizer arm isrotatably connected to the distal end of the housing by a second hingeassembly.
 6. The device of claim 1, wherein the pusher cup has a pusherreceptacle.
 7. The device of claim 6, wherein the pusher receptacle hasa threaded recess configured to threadably receive a top of a pushertool.
 8. The device of claim 1, wherein the stabilizer arm has a corestructure that is torque and compression resistant.
 9. The device ofclaim 1, wherein the appendage arm has a core structure that is torqueand compression resistant.